201130462 六、發明說明： 【發明所屬之技術領域】 本發明係有關於一種睡眠腦波監測裝置，尤其是一種 能藉由即時監控並分析使用者之睡眠腦坡訊號，而=到使 用者睡眠之健康管理之睡眠腦波監測裴置。 【先前技術】 ，-二睡眠品質不佳之問題，為了解決此現象 二;1=收集患者之睡眠腦波，敌採用_的方式 = 解患者之睡眠情形及其品質。然而，這 缺方式不但具有 波訊號，因此無法即時反岸当者之睡眠^判讀患者之腦 調整相應之對使用者之睡眠情形即時 損害患者之徤=置，而導致患者之醫療品料低，甚至 基於上述問題，霄要—t 之腦波訊號’而判斷麵眠二 '即時監控並分析患者 【發明内容】i。眠1之㈣腦波監測裝置。 本叙明係提供—翻眠腦 即時監控並分析患者睡眠時之腦波：置，其主要係藉由 ，療作業内容，並省::糊整後 繁瑣作業，達到增進腦，人貝雜分析腦波的 。貝政率及方便性等功效，為 201130462 其發明目的。 此外，由於本發明之該睡眠腦波監測裝置係為一可捭 式裝置，因此可使病患在家自行使用，達到病患自J 管理之功效，為其又一目的。 健康 為達到前述發明目的？本發明所運用之技術手段 由δ亥技術手段所能達到之功效包含有： 曰 〜-種_腦波監測裝置，包含—訊號感測模組和—運 异桓組。龍I紐職組係供制—判斷時㈤之—腦波气 號。該運算模組係_至該訊號感測模組，並包含一特符 =揭取單元、一腦波相位判斷單元運算單元和一气號 =出琿。該频鋪取單元係計算該财城之至少一 ς t值崎。該腦波相位判斷單福接收該至少—特徵值訊 =並精著比較該至少—特徵值訊號與—比較門檻值來判 波訊號之-A相位簡和—以健號。該運算單 :ί__皮訊號於該A相位訊號和該B相位訊號之間 波觀交_式時間，料算侧賴環交替 二 = 爾晴於該判斷時間之-腦波_交賴式比值。 循产^出埠純接至該運异單元，以供輸出代表該腦波 僱辰父替模式比值之一輸出訊號。 【實施方式】 為讓本發明之上述及其他目的、特徵及優點能更明顯 作1下文特舉本發明之較佳實施例，並配合所附圖式， 作砰細說明如下： 5青參照第1圖，其係繪示根據本發明一較佳實施例所 201130462 述之~睡眠腦波監測裝置的方挽 較佳係為-可攜式裝置，㈣二民腦波監測裝置 算模組2、-顯示單元3和‘虎感測模組卜一運 包含一切$||罝$ ^ 渚存早兀4,其中運算模組2 切釗早兀2〗、一特徵值擷 斷單元23、一運嘗簞亓）4 η 早7^^22、一腦波相位判 槿％】^ & 及―訊號輸出槔25。訊號残測201130462 VI. Description of the Invention: [Technical Field] The present invention relates to a sleep brain wave monitoring device, in particular to a user who can monitor and analyze a user's sleep brain wave signal in real time, and = to the user's sleep Sleep management for sleep management in health management. [Prior technology], - The problem of poor quality of sleep, in order to solve this phenomenon 2; 1 = collect the sleep brain wave of the patient, the way the enemy adopts _ = the sleep situation and quality of the patient. However, this lack of method not only has a wave signal, so it can not immediately sleep on the shore. The patient's brain adjustment corresponding to the user's sleep situation immediately damages the patient's 徤 = set, resulting in the patient's medical supplies are low, Even based on the above problems, I want to monitor the patient's [invention] i. Sleeping 1 (four) brain wave monitoring device. This narration provides an instant monitoring and analysis of the brainwaves of the patient during sleep: the main reason is that the treatment content, and the province:: after the paste, the cumbersome work, to improve the brain, human shellfish analysis Brain wave. The effect of Beizheng rate and convenience is the purpose of 201130462. In addition, since the sleep brain wave monitoring device of the present invention is a portable device, the patient can be used at home to achieve the effect of the patient's self-J management, which is another purpose. Health In order to achieve the aforementioned objectives? The technical means used by the invention The functions that can be achieved by the δHui technology include: 曰 ~- species _ brain wave monitoring device, including - signal sensing module and - 桓 桓 group. The dragon I New team is a system of supply - when judging (5) - brain wave. The computing module is _ to the signal sensing module, and includes a special symbol = stripping unit, a brain wave phase determining unit computing unit, and an air number = output. The frequency paving unit calculates at least one value of the financial city. The brain wave phase judgment unit receives the at least eigenvalue signal and compares the at least the eigenvalue signal with the comparison threshold value to determine the -A phase summation of the signal to the health symbol. The operation list: ί__ pictogram between the A phase signal and the B phase signal _ _ time, the calculation side 赖 ring alternate two = erqing in the judgment time - brain wave _ cross-reference ratio . The output is purely connected to the transport unit for output to represent the output signal of the brain wave hiring father for the mode ratio. BRIEF DESCRIPTION OF THE DRAWINGS The above and other objects, features, and advantages of the present invention will become more apparent from the description of the preferred embodiments of the invention. 1 is a block diagram of a sleepy brain wave monitoring device according to a preferred embodiment of the present invention, which is a portable device, and (4) a two-person brain wave monitoring device calculation module. - Display unit 3 and 'Tiger sensing module Bu Yiyun contains everything $||罝$^ 兀存早兀4, where the computing module 2 is cut as early as 2, a characteristic value smashing unit 23, one transport Taste 箪亓) 4 η early 7^^22, one brain wave phase judgment %] ^ & and ― signal output 槔 25. Signal residual test
杈'，且〗係耦接至運算模組2之 ^ J 切割單元21、特徵㈣取單元2;]:。運算模組_2之 、運算單元24及訊號輸出埠25 ^·早70 23 Μ 1 - , 0q &、串恥褐接於訊號感測模 及如早儿3之間。儲存單元4係 2之喊輪出埠25，销存單以可為且 ' -^m,«(Flash Memory), D(SD;;d) 光健存媒體_㈣S論ge)等i。碟(HardD叫或一 訊號感測模組i係感測一使用者處 皮訊號，並將此腦波訊號傳= 咸、、目丨《<、°早。其中’訊號感測模組1之結構及藉其 二1腦波之方法柄本領域熟悉該技藝者所可以理解 ，使用者之睡眠狀態可區分為四個階段，第—和第二 =段之淺_、第三睡眠階段之深_和第喊眠階段 。无、睡期’該判斷時間可處於任一上述四睡眠階段之期間 兮㈣？算模組2之切割單元21係供接收該判斷時間内之 號’將該判斷時間切割為數個輕時間，並依序 、.二早位時間内之腦波訊號送至特徵值操取單元22 5以 ΐί异ίί2對每—該單位時間内的該腦波訊號個別進行 々°χ單位時間之長度較佳係為Q.4秒(但並不以此為限 201130462 )，且相鄰之二單位時間可具有時間重疊，其較佳係為該單 位時間之50%。舉例來說，假設該判斷時間為一小時，且 母個單位時間之長度為0.4秒，則切割單元21將該判斷時 間切割為17999個單位時間，且相鄰之二單位時間具有 5〇%之時間重疊（亦即0.2秒）。杈', and is coupled to the computing module 2 ^ J cutting unit 21, feature (four) taking unit 2;]:. The operation module _2, the operation unit 24, and the signal output 埠 25 ^· early 70 23 Μ 1 - , 0q &, the string smear is connected between the signal sensing mode and the early 3 . The storage unit 4 is a shouting wheel 25, and the stocking slip can be used as and '-^m, «(Flash Memory), D(SD;;d) optical storage media _(four) S ge) and so on. The disc (HardD or a signal sensing module i senses a user's skin signal and transmits the brainwave signal = salty, and the video "<, ° early. Among them" signal sensing module 1 The structure and the method of the second brainwave can be understood by those skilled in the art that the sleep state of the user can be divided into four stages, the shallowness of the first and second = paragraphs, and the depth of the third sleep stage. _ and the first sleep stage. No, sleep period 'The judgment time can be in any of the above four sleep stages 兮 (four)? The cutting unit 21 of the calculation module 2 is for receiving the number of the judgment time 'the judgment time The cutting is performed for several light times, and the brain wave signals in the second morning time are sent to the characteristic value operation unit 22 5 to 个别 异 异 ί ί 对 每 每 每 每 每 χ χ χ χ χ χ χ χ χ χ χ χ χ χ χ χ χ χ χ χ χ χ χ χ The length of the unit time is preferably Q.4 seconds (but not limited to 201130462), and the adjacent two unit time may have time overlap, which is preferably 50% of the unit time. For example , assuming that the judgment time is one hour, and the length of the parent unit time is 0.4 seconds, then cut The cutting unit 21 cuts the judgment time into 17999 unit time, and the adjacent two unit time has a time overlap of 5% (i.e., 0.2 second).
特徵值擷取單元22分別為各該單位時間之該腦波訊 號計算一特徵值訊號。其中’該特徵值訊號係可為該腦波 訊號在該單位時間内之平均值、平均絕對誤差、均方根值 、變異數、標準差或上述各數值之任意組合。亦即，針對 任一單位時間，特徵值擷取單元2 2係計算此一單位時間之 特徵值訊號。 、腦波相位判斷單元23係對應於該特徵值訊號之取值 方式預先設定一比較門檻值TH，且當該特徵值訊號大於該 比較門檻值TH時，腦波相位判斷單元23判斷該單位時間 内之該腦波訊號係為-A相位訊號；反之，當該特徵值訊 號小於該比較門權值TH時，腦波相位判斷單元23判斷該 特定單位日之該腦波訊號係為—B相位訊號。詳言之， S玄比較門棰值TH係可根據以下公式計算. 比較門榧值TH:該判斷時間所處:睡眠階段之該腦 =號的-特徵《 +K*該判斷時間所處之睡眠階段之 3玄取波訊號的一變異特徵。 ，比係與該特徵值訊號類似 …白可為雜皮訊號在特定睡眠階段之平均值、平均絕對 方根值、變異數、標準差或±述各數值之任意組 曰等等。舉例來說，在一實施方…、’ 貝她万式中，假設該判斷時間係 201130462 處於弟三睡眼卩比 睡眠過程中之深輸，則藉由絲已記錄之前-次 的腦波訊號來t!1號，可使用該使用者之第三睡眠階段 ..ptbin.. ’、疋5亥特徵門檻，且該特徵門檻係為第三睡 有腦波訊號之平均值、平均絕對誤差、均方根 值、變異數、巧 ，在另—每〃不半差或上述各數值之任意組合等等。或者 汽^方式中，若欲針對該第三睡眠階段之深睡期 之内的判斷時間渔 ， 一 、 進订判斷，但無該使用者先前已記錄之前 “ 中的腦波訊號可供參考，即可預先設定時間 ％ ^㈣斷日^"間之—預定時間，以該預定時間内之腦 ^、平均值、平均絕對誤差、均方根值、變異數、標 / 5其任思、組合等當成該特徵門檻。 在上述比較門植值ΤΗ的公式巾，κ為一變異特徵係 文’其值對應於第—和二睡眠階段係設A 1，對應於第三 垂民卩白奴(丁又為】5，以及對應於第四睡眠階段係設為2。 ，外’皮訊號之變異特徵係可透過標準差、變異數、 或其他可代表該腦波訊號之變異特性的特徵訊號求得。據 此i腦波相位判斷單元23逐—判斷各該單位時間之該腦波 吼號的相位(屬於A相位訊說和B相位訊號），並將所判斷 之結果送至運异單元24 =請參照第2圖，其係繪示該使用 者腦波訊號之一範例。在第2圖的範例中，位於該腦波訊 號之一左方星號與右方星號，，*，，中間的區段係為該A相 位讯唬，而位於此區段之外的腦波訊號係屬於該B相位訊 號。 運异單元24係接收腦波相位判斷單元23之輸出結果 ，計算該判斷時間内之一腦波循環交替模式（Cyclic 201130462The feature value capturing unit 22 calculates a feature value signal for each brain wave signal of the unit time. Wherein the characteristic value signal is an average value, an average absolute error, a root mean square value, a variance number, a standard deviation or any combination of the above values of the brain wave signal in the unit time. That is, for any unit time, the feature value extracting unit 2 2 calculates the characteristic value signal of the unit time. The brain wave phase determining unit 23 presets a comparison threshold TH corresponding to the value of the feature value signal, and when the feature value signal is greater than the comparison threshold TH, the brain wave phase determining unit 23 determines the unit time. The brain wave signal is a -A phase signal; otherwise, when the feature value signal is smaller than the comparison gate weight TH, the brain wave phase determining unit 23 determines that the brain wave signal of the specific unit day is -B phase Signal. In detail, the S threshold comparison threshold TH can be calculated according to the following formula. Comparison threshold TH: The judgment time is: the brain = number of the sleep stage - feature " + K * the judgment time is A variation feature of the 3 stages of the sleep stage. The ratio is similar to the eigenvalue signal. White can be the mean value, the average absolute root value, the variance, the standard deviation, or any of the various values of the noise signal at a particular sleep stage. For example, in an implementation..., 'Bei-Wan Wan, suppose that the judgment time is 201130462, which is in the deep sleep of the third sleepy eye than the sleep process, then the silk wave signal has been recorded before the silk has been recorded. t! No. 1, the third sleep stage of the user can be used.. ptbin.. ', 疋5hai characteristic threshold, and the characteristic threshold is the average value of the third sleepy brain wave signal, the average absolute error, both The square root value, the variation number, the skill, and the other - each half is not half difference or any combination of the above values, and the like. Or in the steam mode, if it is desired to judge the time fish within the deep sleep period of the third sleep stage, the decision is made, but no brain wave signal is available for reference before the user has previously recorded. You can pre-set the time % ^ (four) break the day ^ " between - the scheduled time, the brain within the predetermined time ^, the average, the average absolute error, the root mean square value, the variance, the standard / 5, Ren Si, The combination is regarded as the threshold of the feature. In the above formula for comparing the planting value, κ is a variant characteristic text 'the value corresponding to the first and second sleep stages is set to A 1, corresponding to the third sacred white slave (Ding is also 5), and corresponding to the fourth sleep stage is set to 2. The external 'skin signal's variability characteristics are through standard deviation, variation, or other characteristic signals that can represent the variation characteristics of the brainwave signal. According to this, the i-brain wave phase judging unit 23 judges the phase of the brain wave semaphore (the A-phase speech and the B-phase signal) of each unit time, and sends the result of the judgment to the transport unit. 24 = Please refer to Figure 2, which shows the user An example of the wave signal. In the example of Figure 2, the segment between the left asterisk and the right asterisk, *, , in the brainwave signal is the A phase, and is located in this segment. The brain wave signal other than the brain signal belongs to the B phase signal. The transport unit 24 receives the output result of the brain wave phase determining unit 23, and calculates one of the brain wave cycle alternating modes in the judgment time (Cyclic 201130462)
Alternating Pattern，CAP)時間（CAP time)，並進一步計管 該CAP時間相對於該判斷時間之百分比值以做為一腦波 循環交替模式比值(CAP rate) ’最後再產生—輸出訊號由訊 號輸出璋25輸出。詳言之，當該判斷時間内之各該單位時 間之該腦波訊號的相位皆為已知之情況下，運算單元24 計异獲得該CAP時間的方式較佳係如下所述。運算單元 24首先進行一校正步驟，以檢閱任一 b相位訊號的持續時 間疋否小於一調整時間，若結果為「是」即將此一B相位 訊號的判斷結果調整為A相位訊號。其中，該調整時間係 供根據習知之腦波訊號之規律性調整腦波相位判斷單元 23之誤判結果，且該調整時間之長度較佳係 繼之’運算單元24進行-循環交替模式判斷㈣，其係判 斷各5¾ B相位號的持續時間是否小於一標準時間，若此 判斷結果為「是」即將前- A相位訊號及該B相位訊號的 總持續時間定A為-相位交替時間；岭此判斷結果為「 否」則將鈾一 A相位汛號之持續時間及該標準時間定義 ，該相位交替時間，其中該標準時間較佳係設定為6〇秒。 藉此’運算單元24即可將該判斷時間内的戶斤有相位交替時 間進行加總而獲得該CAP時間。最後，再將該CAp時間 除以該判斷時間以取得該CAp比值。此外，該訊號輸出璋 5，輸出之輸出職即表示該CAP比值，且該⑽比值 之冋低代表該使用者之睡眠的深淺程度。詳言之，一般而 =f該CAP比值高於時’代表該使用:處於較淺又的 中’·反之’當該CAP比值低於4〇%時，即代表該 使用者處於較淥沉的睡眠狀態中。 201130462 據此任何連接於訊號輸出埠25的電子醫療儀器即 可根據訊號輸出埠25之輸出訊號進行醫藥劑量或者醫學 療程的調整，達到根據即時偵測之睡眠腦波迅速調整醫療 内容之目的。舉例而言，當連接於訊號輸出埠25之電子醫 療儀器為一正壓輔助呼吸裝置時’該正壓輔 : 可預設至少一氣壓輸出等級，以便在接收訊號;^璋置 之輸出訊號之後，對應於不同的腦波循環交#模式比例值 輸出純數值之氣壓。·：當賴賴環交替模式比例 值較高時’即表示該使用者之_狀錄淺，故該正壓輔 助呼吸裝置可對應提高氣壓輸料級，以增加輸出之氣壓 值而促使該制者再次賴至㈣深㈣_狀能。反之 玄的腦波循環交替模式比例值較低時，該正壓輔助呼 吸裝置可對應降低氣壓势+ 避勞、幸出 条低輸出之氣壓值， 避免過度⑽毛§亥正壓辅助呼吸袭置之儲氧量。 此外’連接至訊號輪出蜂25之顯 該輸出訊號，並顯示運首 係可接收 替模式比例值。另，^^ ^十异㈣之腦波循環交 B和運算單元24州^=組]，她判斷單元 此-來，顯示單元3亦=至，單f 3和儲存單元心如 位訊號和該B相位訊心=訊號之態樣、該A相 交替模式比例值。同時二忙，矣情形’以及該腦波猶環 之態樣、該A相位訊號和4亦可健存該腦波訊號 以及該财循環交替楛^目位崎之間的切換情形， 分析判斷之用。 …祕1供後續進行其他醫療 根據本發明之該睡眠腦波監職置，可省略醫護人員 10 201130462 需事後分析腦波的歌 功效。料，由於^ 進料_方便性之 ，因此可使病患在家監=置:為〜可攜式裝置 功效。 吏711，達到病心自我健康管理之 雖然本發明已利用卜. ^ ^ ^ ± ^ BB , 以較仏貫轭例揭示，然其並非用 二、本杳明，任何熟習此技藝者在不脫離本發明之精神 和範圍之内，相對上述實施例進行各種更動與修改仍屬本Alternating Pattern, CAP) time, and further calculate the percentage value of the CAP time relative to the judgment time as a brain wave cycle alternating mode ratio (CAP rate) 'last reproduced—output signal is output by signal璋25 output. In detail, when the phase of the brain wave signal at each unit time in the judgment time is known, the manner in which the arithmetic unit 24 calculates the CAP time is preferably as follows. The operation unit 24 first performs a correction step to review whether the duration of any of the b-phase signals is less than an adjustment time. If the result is "YES", the judgment result of the B-phase signal is adjusted to the A-phase signal. The adjustment time is for adjusting the false positive result of the brain wave phase judging unit 23 according to the regularity of the conventional brain wave signal, and the length of the adjustment time is preferably followed by the operation unit 24 performing the loop alternating mode judgment (4). It is determined whether the duration of each of the 53⁄4 B phase numbers is less than a standard time. If the result of the determination is "Yes", the total duration of the front-A phase signal and the B-phase signal is determined to be - phase alternating time; If the judgment result is "No", the duration of the uranium-A phase nickname and the standard time are defined, and the phase alternate time, wherein the standard time is preferably set to 6 sec. By this, the arithmetic unit 24 can add the phase alternate time of the households in the judgment time to obtain the CAP time. Finally, the CAp time is divided by the judgment time to obtain the CAp ratio. In addition, the signal output 璋 5, the output output of the output indicates the CAP ratio, and the lower of the (10) ratio represents the degree of sleep of the user. In detail, generally, if the CAP ratio is higher than 'represents the use: in the shallower one', the other way, when the CAP ratio is lower than 4〇%, it means that the user is in a dignified position. In sleep state. 201130462 According to this, any electronic medical instrument connected to the signal output 埠25 can adjust the medical dose or medical treatment according to the output signal of the signal output 埠25, so as to quickly adjust the medical content according to the sleep brainwave detected by the instant detection. For example, when the electronic medical device connected to the signal output port 25 is a positive pressure auxiliary breathing device, the positive pressure auxiliary device can preset at least one air pressure output level so as to receive the signal after the output signal is received. Corresponding to the different brainwave cycle intersection # mode proportional value output pure value of the air pressure. · When the proportional value of the alternating mode of the Lai-Ring ring is high, it means that the user's _ record is shallow, so the positive-pressure assisted breathing device can increase the pressure-feeding level to increase the pressure value of the output to promote the system. The person once again relies on (four) deep (four) _ shape energy. On the other hand, when the proportional value of the alternating brainwave cycle mode is low, the positive pressure assisted breathing device can reduce the barometric pressure + avoidance, and the low output pressure value of the lucky bar, avoiding excessive (10) Mao § 正 positive pressure assisted breathing The amount of oxygen stored. In addition, the output signal connected to the beacon 25 is displayed, and the display mode can receive the ratio value of the mode. In addition, ^^ ^ ten different (four) brain wave cyclic B and the arithmetic unit 24 state ^ = group], she judges the unit - this, display unit 3 also = to, single f 3 and storage unit heart as the signal and B phase heart = the state of the signal, the proportional value of the A phase alternate mode. At the same time, the second is busy, the situation is 'and the brain wave is still ringing, the A phase signal and 4 can also save the brain wave signal and the switching between the financial cycle and the position of the target, analyze and judge use. ... Secret 1 for subsequent medical treatment According to the sleep wave of the present invention, the medical staff can be omitted. 10 201130462 It is necessary to analyze the effect of the brain wave afterwards. Because of the convenience of feeding, it can make the patient monitor at home: it is a portable device.吏 711, to achieve the self-health management of the disease heart, although the present invention has utilized Bu. ^ ^ ^ ± ^ BB, to reveal more than the yoke example, but it is not used in the second, this 杳明, any familiar with this skill is not separated Within the spirit and scope of the present invention, various changes and modifications to the above embodiments are still
發明所保護之技術範《壽，因此本發明之保護範圍當視後附 之申請專利範圍所界定者為準。 201130462 【圖式簡單說明】 第1圖：本發明一較诖實施例所述之一睡眠腦波監測裝 置的方塊圖。 第2圖：本發明較佳實施例所述之一使用者腦波訊號之 範例。 【主要元件符號說明】 〔本發明〕 1 訊號感測模組 2 運算模組 21 切割單元 22 特徵值擷取單元 23 腦波相位判斷單元 24 %«* xyV — 運具早兀 25 訊號輸出埠 3 顯示單元 4 儲存單元The technical scope of the invention is protected by the invention, and therefore the scope of protection of the invention is defined by the scope of the appended claims. 201130462 [Simplified description of the drawings] Fig. 1 is a block diagram of a sleep brain wave monitoring device according to a comparative embodiment of the present invention. Fig. 2 is a diagram showing an example of a user brain wave signal according to a preferred embodiment of the present invention. [Description of main component symbols] [Invention] 1 Signal sensing module 2 Operation module 21 Cutting unit 22 Characteristic value capturing unit 23 Brain wave phase judging unit 24 %«* xyV - Equipped with early 25 signal output 埠 3 Display unit 4 storage unit