201120439 六、發明說明： 【發明所屬之技術領域】 本發明係關於-種電化學生物感測試紙，尤指—種於基板背 面-端設有-錄韻元細能免錢財進脖倾正步驟之 電化學生物感測試紙。 【先前技術】 由於科技的進步，過去許多必須在醫院才能進行檢測的試 驗，現在大？走向絲職的方向。目前市面上有許多用過一次 後即可丟棄且用於居家自行操作之生物感測試紙，適合非專業人 員及居家護雜用’不會有污染的情形發生，並且配合適當的生 物感測器裝置，即可測量出正媒的測量數值。 以血糖檢測技術為例，由於具有操作便利與及時檢驗的優 點’血糖機近年來已成為臨床與居家照護作業中普遍使用的床邊 檢測(Point of care test，P〇CT)醫療器材之一。根據台灣糖尿 病學會的統計齡說明’目前市售血糖機的分析原理，主要是利 用電化學(Amperometric electrochemistry)原理進行測試；當血 液中葡萄糖與電化學生物制試紙上之酵素產生電化學反應後， 借由介質電子轉出’透過血糖機將電流變化轉換為血糖濃度數 值。 習用之電化學生物感測試紙具有一基板、一導電層、—反應 201120439 區及一上隔板，在該基板上形成導電層，該導電層包含二條分離 且互不相接觸的陽極部分和陰極部分，在該導電層上局部覆蓋一 層電絕緣層而裸露出部分導電層，該導電層陽極及陰極裸露出之 部分一端形成工作電極及參考電極，而另一端則可與生物感測器 裝置連接，並在該工作電極及參考電極上覆蓋一反應區，該反應 區視不同原理而製作，並於反應區上覆蓋一上隔板。當樣品吸入 後，樣品即會與反應區物質發生反應並產生電化學變化，而由工 _作電極與參考電極傳導至導電層另一端之陰極接頭與陽極接頭， 藉由與生物感測器裝置連接並接收訊號，經過計算而將訊號轉換 成待測物濃度顯示於一顯示器上。 然而，由於電化學生物感測試紙目前皆以批量生產（匕扣比 production)之方式製造，因此製造過程中的各項變因將造成每批 試紙間的差異性’例如卫作電極與參考電極的體積、反應區内的 鲁酵素量等，皆會影響檢須榑致測量結果不準確。因此血糖機專用 試紙出廠前，廠商會依據每一批號的產品設定一組特定的校正參 數值’以確嫌齡析值的—致性。血糖_諸陳正作用即 在於確認試紙不會因為製造批號不同，而有不同的分析結果。 目別市售血練内參數校正方法主要有“設定法、試紙編 號核對法等。以⑼設定法糊n錄試紙在開始使用前， 都必須先以内附的晶片來校正血糖機内之參數，然而病患或實施 測置的家屬卻時常忘記這個校正動作，導剌量得出之血糖值不 5 201120439 甚準確而不自知。美國發明專利公開號第2〇〇3〇2〇4313號所提供 之一種可利用參數校正試紙進行參數校正之生物感測器裝置，其 參數校正方式便與此近似。而美國發明專利第7 514 〇4〇號係 關於一種可内建參數密碼亦可外掛參數密碼的智慧型生物感測器 裝置，其於生物感測器裝置内建數組校正參數值，使用者於進行 測量前須先選定與該批試紙相配合之參數值，其參數校正方式係 屬於試紙編號核對法。 如先前技術t所提及，不論血糖機使用現行任何一種參數校 正方式，皆需要額外增加使用者的操作步驟，導致檢測程序上的 繁瑣，且使用者一旦疏漏或未正確執行該校正步驟，則無法得到 正確之檢猶果m費時間與資源，更對病患之生活與健康 官理造成負面影響。依據糖尿病衛教學會2〇〇6年調查統計顯示， 32. 9%的病患錯誤使用血糖機，包括使用前忘記校正導致測量不 準確’影響血糖㈣。前述缺失對伽者造成之錢，由此可見 -斑。因此’如何簡化甚至省去使用者在測量前的校正步驟，但 仍能維持測量結果之準確性，乃為相關業者爾改進之處。 【發明内容】 名詞定義 生物感測器裝置 係指與本發明所提供之電化學生物感測試紙相配合以檢測一 201120439 樣本中特物質濃度之裝置，如血糖儀、膽目醇儀、尿酸儀等。 感測器端 係指本發明所提供之電化學生祕測試紙於使用時與生物感 測器装置相接觸之一端。 反應端 係指本發騎提供之電化學生械測試紙於時與樣本進 行反應之-端’通常即反應區所在之—端，並相對於感測器端。 如先刖技術中所提及，為了省去使用者在測量前的校正步 驟’但仍轉制量結果之準雜，本㈣係提供—種電化學生 :勿感測試、A ’其巾包含於基板背面—端之參數辨識元件，使 該試紙與生物_!!裝置連接時即可自_擇相對應於該批試紙 組校正參數值’進而省去由使用者執行的參數校正步驟，簡 化整體測量程序’避免使用者因疏漏或操作錯誤而導致不準確之 檢測結果。 本發明之技術核在練供-種統學錄❹彳觀，其係 包3 -基板’係設有—正面及—背面；—導電層，餅該基板正 之上，參數辨識元件，設於該基板背面之一端且用以對應一 組特疋之；^正參數值；_上隔板，覆蓋於該導電層之上；以及一 反應區，與該導電層接觸且用以進行反應。 於本發明之較佳實施例甲，本發明所提供之電化學生物感測 試紙中之參數辨識树包含四個以上之不同區塊，透過各區塊之 201120439 相互連通或駐，該紐_树可軸魏 每一態樣係對應於-組特定之校正參數值，故當具且 識元件態樣之試紙與-生物感測器裝置連接時，該裝置^自^ 選擇與該批試紙相對應之一組校正參數值。 於更佳實關巾，本㈣所提供之魏學生物_試紙中之 參數辨識元件包含-第-區塊、—第二區塊、—第三區塊及一第 四區塊等四値塊。藉由該四舰塊之相互連通或獨立，本發明 中之參數辨識元件可形成14種不同之態樣，且每―祕係對應於 一組特定之校正參數值。 本發明所提供之電化學生物_試㈣之參數韻元件係可 由導體所城π齡倾射，該錄觸树軸销組成， 且參數辨識元件各區制之連通觸立係透過雷射侧或刀具餘 刻加以區隔定義。於較佳實施财，該參數辨識元件係設於基板 之感測器端背面。 於本發明所提供之電化學生物感測試紙中，該導電層包含至 少三個電極，且其中至少-電極具有—可變長度區。該可變長度 區係用以辨認與該電化學生物感測試紙相配合之一生物感測器裝 置。藉由改變電極之長度，可調整該電極之電阻值，當該電化學 生物感測試紙與一生物感測器裝置相連接時，透過電阻值之測 量，可用以辨認相配合之生物感測器裝置。於較佳實施例中，該 可變成長度區具有四種不同長度，故可辨認四種不同之生物感測 器裝置。此外，於更佳實施例中，具有該可變長度區之電極係作 201120439 為一參考電極。 於本發明所提供之電化學生物感測試紙中，該導電層包括— 導電銀膠層及-導電碳粉層’且該導電碳粉層覆蓋於該導電轉 層之上。每個導電層電極係由相應之導電碳粉層電極與導電銀膠 層電極所域。例如，導電層第一電極係由導電銀膠層第1極 與導電碳粉層第-電極所組成，導t層第二電極係由導電轉層 第二電極與導電碳粉層第二電極所組成，依此類推。201120439 VI. Description of the Invention: [Technical Field of the Invention] The present invention relates to an electrochemical biosensor test paper, in particular, a substrate-back end-end is provided with a recording rhyme element fine energy-free money into the neck tilting step Electrochemical biosensor test paper. [Prior Art] Due to advances in technology, many tests that must be performed in hospitals in the past are now large? Going to the direction of the job. At present, there are many bio-sensing test papers that can be discarded after one use and used for home operation. It is suitable for non-professionals and home care. It will not cause pollution and cooperate with appropriate biosensors. The device can measure the measured value of the positive medium. Taking blood glucose testing technology as an example, it has the advantage of convenient operation and timely inspection. The blood glucose meter has become one of the point-of-care (P〇CT) medical devices commonly used in clinical and home care operations in recent years. According to the statistical age of the Taiwan Diabetes Association, 'the analysis principle of the currently commercially available blood glucose machine is mainly based on the principle of electrochemical (Amperometric electrochemistry); when the blood glucose reacts with the enzyme on the electrochemical biotest paper, By electronically transferring out the medium's blood glucose level to convert the current change into a blood glucose concentration value. The conventional electrochemical biosensor test paper has a substrate, a conductive layer, a reaction 201120439 region and an upper separator, on which a conductive layer is formed, the conductive layer comprising two anode portions and a cathode which are separated from each other and are not in contact with each other. In part, the conductive layer is partially covered with an electrically insulating layer to expose a portion of the conductive layer. The exposed portion of the anode and the exposed portion of the conductive layer form a working electrode and a reference electrode, and the other end is connected to the biosensor device. And covering the working electrode and the reference electrode with a reaction zone, the reaction zone is made according to different principles, and an upper partition plate is covered on the reaction zone. When the sample is inhaled, the sample reacts with the reaction zone material and produces an electrochemical change, and the electrode and the reference electrode are conducted to the cathode and anode contacts at the other end of the conductive layer, and the biosensor device is used. Connect and receive the signal, and calculate the signal to convert the measured object concentration to a display. However, since electrochemical biosensor test papers are currently manufactured in batch production, the various factors in the manufacturing process will cause differences between each batch of test papers, such as the electrode and reference electrode. The volume, the amount of Lu enzyme in the reaction zone, etc., will affect the inaccuracy of the measurement results. Therefore, before the blood glucose meter test strips are shipped from the factory, the manufacturer will set a specific set of calibration parameter values according to the products of each batch number to determine the value of the age-appropriate value. The role of blood sugar _ Chen Chen Zheng is to confirm that the test paper will not have different analysis results because of the different manufacturing batch numbers. The main methods for correcting the parameters of the blood in the market are “setting method, test paper number verification method, etc.. (9) Setting the method of the method must first use the attached wafer to correct the parameters in the blood glucose meter. The patient or the family member who performed the measurement often forgets the corrective action, and the blood glucose value obtained by the guide volume is not accurate. It is not accurate and does not know. US Patent Publication No. 2〇〇3〇2〇4313 A biosensor device that can perform parameter correction using a parameter correction test strip has a parameter correction method similar thereto. The U.S. invention patent No. 7 514 〇 4 关于 relates to a built-in parameter password or an external parameter password. The intelligent biosensor device has an array correction parameter value built in the biosensor device, and the user must select a parameter value matching the batch test paper before performing the measurement, and the parameter correction mode belongs to the test paper number check. As mentioned in the prior art t, no matter whether the blood glucose meter uses any of the current parameter correction methods, it is necessary to additionally increase the user's operation steps, resulting in The cumbersome testing procedure, and if the user misses or does not correctly perform the correcting step, it will not be able to get the correct time and resources, and it will have a negative impact on the life and health of the patient. According to the survey statistics of 2-6 years of teaching, 32.9% of the patients mistakenly use the blood glucose machine, including forgetting the correction before use, resulting in inaccurate measurement 'affecting blood sugar (4). The above-mentioned missing money caused by the gamma, thus visible - Therefore, 'how to simplify or even eliminate the user's calibration steps before the measurement, but still maintain the accuracy of the measurement results, is the improvement of the relevant industry. [Invention] The term definition biosensor device refers to A device for detecting a concentration of a specific substance in a sample of 201120439, such as a blood glucose meter, a cholesterol meter, a uric acid meter, etc., in combination with the electrochemical biosensor test paper provided by the present invention. The sensor end is provided by the present invention. The electrochemical biopsy test paper is in contact with the biosensor device at the end of the use. The reaction end refers to the electrochemical bio-test paper provided by the hair ride and the sample. The end of the reaction is usually the end of the reaction zone and is relative to the sensor end. As mentioned in the prior art, in order to save the user the calibration step before the measurement, but still the result of the conversion Quasi-heterogeneous, this (4) provides an electrochemical life: no sense test, A 'the towel is included in the back side of the substrate - the parameter identification component, so that the test paper and the biological _!! device can be selected from The batch of test strips corrects the parameter value 'and further eliminates the parameter correction step performed by the user, simplifies the overall measurement procedure 'avoiding inaccurate detection results caused by the user due to omission or operational error. The technology of the present invention is in practice - In the case of the genre, the 3-package is provided with a front surface and a back surface; a conductive layer is directly above the substrate, and a parameter identification component is disposed at one end of the back surface of the substrate and is adapted to correspond to a a characteristic parameter; a positive parameter value; an upper spacer overlying the conductive layer; and a reaction region in contact with the conductive layer for reacting. In a preferred embodiment of the present invention, the parameter identification tree in the electrochemical biosensor test paper provided by the present invention comprises four or more different blocks, which are interconnected or resident through the 201120439 of each block. Each axis of the axis corresponds to a group-specific calibration parameter value, so when the test piece having the component component is connected to the biosensor device, the device is selected from the group corresponding to the batch of test paper. One group corrects the parameter value. In the more practical cover towel, the parameter identification component in the Wei student object _ test paper provided in this (4) includes - the first block, the second block, the third block and a fourth block. . By the interconnection or independence of the four blocks, the parameter identification elements of the present invention can form 14 different aspects, and each "secret" corresponds to a specific set of correction parameter values. The parameter of the electrochemical bio-test (4) provided by the present invention can be formed by the π-age of the conductor, the recording tree axis pin, and the connected contact system of each parameter of the parameter identification component passes through the laser side or The tool is always defined by the interval. Preferably, the parameter identification component is disposed on the back side of the sensor end of the substrate. In the electrochemical biosensor test paper provided by the present invention, the conductive layer comprises at least three electrodes, and wherein at least - the electrode has a variable length region. The variable length zone is used to identify a biosensor device that is compatible with the electrochemical biosensor test paper. By changing the length of the electrode, the resistance value of the electrode can be adjusted. When the electrochemical biosensor test paper is connected to a biosensor device, the measurement of the transmission resistance value can be used to identify the matching biosensor. Device. In the preferred embodiment, the variable length zone has four different lengths so that four different biosensor devices are identifiable. Moreover, in a more preferred embodiment, the electrode having the variable length region is used as a reference electrode in 201120439. In the electrochemical biosensor test paper provided by the present invention, the conductive layer comprises a conductive silver paste layer and a conductive carbon powder layer, and the conductive carbon powder layer covers the conductive conductive layer. Each of the conductive layer electrodes is formed by a corresponding conductive carbon powder layer electrode and a conductive silver paste layer electrode. For example, the first electrode of the conductive layer is composed of a first electrode of the conductive silver paste layer and a first electrode of the conductive carbon powder layer, and the second electrode of the conductive t-layer is composed of a second electrode of the conductive conductive layer and a second electrode of the conductive carbon powder layer. Composition, and so on.
於本發明所提供之電化學生物感測試紙中，該導電層之電極 内縮’使導電層於感測器端之末端與該基板於感測器端之末端相 距〇. 1至1公厘’以避免電化學生物感測試紙在正確地插入生物 感測器裝置前便啟動該裝置。 於較佳實施例中，該導電層包含五個電極，分別為—導電 層第-電極、-導電層第二電極、—導電層第三電極、一導電層 第四電極與導電層第五電極，且該五個電極於感測器端皆呈縱 向且彼此相互平行。其中該導電銀膠層第二電極具有—可變長产 區’用以辨認與該統學生物感職_配合之生物感測器ς 置。且該導電層之五個電極中的細個電極相連接形成短路姓 構，該短路結構可啟動相符合㈣則貞測試紙檢測結果口 的生物感測器裝置。於更佳實施例中，該導電層之第二電極與 第三電極相連接形成短路結構，並共同做為—參考電極。、 、'、另/更佳實施例巾，該導電層第—電極與該導電層第二電 極相連接形成贿結構’料驗為—參考電極。 201120439 於本發明所提供之電化學生物感測試紙中，該導電層包含至 少三個電極’其中至少—個電極絲考電極，且其中至少一個電 極為工作電極。於較佳實施财，該導電層包含五個電極，其中 兩《極相連接形成-共狀參考電極，另兩個電極為工作電 極’分顧以制樣本中之血糖值與血容比；且另―電極為_ 電極，用㈣雖本衫已完全進人反顧。於更佳實施例中， 該導電層包含五_極’其中該導電層第二電極與該導電層第三 電極相連接形成-制之參考雜，料電層第四電極為摘測電 極’而該導電層第-電極與該導電層第五電極為卫作電極。 於另一更佳實施例中，該導電層包含五個電極，其中該導電 層第-電極與該導電層第二電極相連接形成—共用之參考電極， 該導電層第三電極為制電極，而該導電層第四電極與第五電極 為工作電極。 於本發明所提供之電化學生物感測試紙中，該基板之四個角 係為鈍角’以避免使用者於操作時不慎被基板尖端刺傷或割傷。 於本發明所提供之電化學生物感測試紙中，進一步包含一覆蓋 於導電層及部分基板±之巾隔板’且該巾隔板於反應端設有一凹 槽，呈縱向且開口向該反應端。該中隔板另設有一開口，該開口 係相鄰於該凹槽且與該凹槽間不相互連通，並對應於該反應區。 於本發明所提供之電化學生物感測試紙中，該上隔板相應於 中隔板之開口處設有一用以通氣之開孔。且該上隔板於反應端設 有一缺口，於較佳實施例中，該缺口呈半圓形或半橢圓形。 201120439 另外’於本發囑提供之電化學生物_試財，該導電碳 粉層於反應端外侧設有一粗糙段。該粗糙段為複數段直線，其係 用以增加基板的粗糙度，防止反颜物f脫落，增加檢測的準確 性0 於本發明所提供之電化學生物感測試紙中，進一步包含一介 於該中板及該上隔板間之黏膝層，用以接合該上隔板=中隔 板’且該黏膠層相應於該中隔板之凹槽及開口處設有一第二凹 •槽。於本發明所提供之電化學生物感測試紙中，可再進一步包含 一介於該導電層及該中隔板間之絕緣層，其中該絕緣層相應於該 中隔板之凹槽及開口處設有一第三凹槽。 綜上所述，本發明所提供之電化學生物感測試紙對照於先前 技術與現有之產品，具有以下之有利功效： -、本發騎提供之電化學生物_試紙與生物_器裝置連接 時即可_裝置自_擇姆應於該減紙之—錄正參數 值，進而料由使用者執行的參數校正步驟，簡化整體測量 程序’避免因使用者疏漏或操作錯誤而導致不準確之檢測結 果。 免去需使用晶片卡進行校正所需之麟製造成本。 三、將參數_元件餘絲之扣，聽鮮㈣共置於基板 正面’降低試紙與相配合生物感測器裝置於機構設計上之複 雜程度與製造成本。 透過可變長度之電極以辨認與該試紙相配合之生物感測器裝 201120439 置，增加使用上之方便性。 本發明内容及若干類實關請參考_且詳述如下。事實 上，本發明可能料_形絲實施，且残频推斷為僅限於 文中所提及的實例。 ' 【實施方式】 第-圖、第二圖及第三圖所示分別為本發明第—種實施例之 立體分解®、立體上視®及立體下視圖。如第—圖至第三圖所示， 本發明所提供之f化學生物感測試紙包含—基板⑽，係設有一 正面（及-背面⑽）；-導電層⑽，設於該基板⑽正面 (102)之上；-參數辨識元件⑽，設於該基板⑽背面⑽)之 -端且用崎應-組之校正參數值；—上隔板⑽覆蓋於 該導電層⑽之上；以及-反應區⑽），與該導電層⑽接觸且 用以進行反應。此外，本發衝提供之電化學生物_試紙可進 一步區分為一感測器端（91)及一反應端（92)。 本發明所提供之電化學生物感測試紙中，該基板（1〇)可為 一矩形片體，較佳地為具有電絕緣特性。於較佳實施例中，該基 板〇0)之四個角係為鈍角（12)，以避免使用者於操作時不慎被尖 端刺傷或割傷。該導電層（2〇)塗佈於基板（1〇)正面⑽)上， 且該導電層包括一導電銀膠層（22)及一導電碳粉層（24)，該導 電碳粉層（24)覆蓋於導電銀膠層（22)上。而該導電層（20) 至少包含二條電極，該三條電極中至少包括一工作電極及一參考 12 201120439 電極。於較佳實施例中，該導電層（20)於該感測器端（91)與基 板（10)之長邊呈縱向且彼此呈平行，其係用以與生物感測器裝 置相接觸而偵測電化學之改變。 於較佳實施例中，該導電層（20)之電極内縮，使該導電層（2〇) 於感測器端（91)之末端與該基板（1〇)於感測器端（91)之末端相距 0.1至1公厘’以避免電化學生物感測試紙在正確地插入生物感測 器裝置前便啟動該裝置。於更佳實施例中，該導電層（2〇)於感測In the electrochemical biosensing test paper provided by the present invention, the electrode of the conductive layer is indented such that the end of the conductive layer at the end of the sensor is at a distance from the end of the substrate at the end of the sensor. 1 to 1 mm. 'To prevent the electrochemical biosensor test paper from starting the device before it is properly inserted into the biosensor device. In a preferred embodiment, the conductive layer comprises five electrodes, a conductive layer first electrode, a conductive layer second electrode, a conductive layer third electrode, a conductive layer fourth electrode, and a conductive layer fifth electrode. And the five electrodes are longitudinal in the sensor end and parallel to each other. The second electrode of the conductive silver paste layer has a variable length producing area for identifying a biosensor device that cooperates with the student. And the thin electrodes of the five electrodes of the conductive layer are connected to form a short circuit structure, and the short circuit structure can activate the biosensor device in accordance with (4) the test paper detection result port. In a further embodiment, the second electrode of the conductive layer is connected to the third electrode to form a short-circuit structure and collectively serves as a reference electrode. And, the other/better embodiment towel, the first electrode of the conductive layer is connected to the second electrode of the conductive layer to form a bribe structure as a reference electrode. In the electrochemical biosensor test paper provided by the present invention, the conductive layer comprises at least three electrodes, at least one of which is a wire electrode, and at least one of which is an electrode. Preferably, the conductive layer comprises five electrodes, wherein two "poles are connected to form a co-reference electrode, and the other two electrodes are working electrodes" to make a blood glucose value to a blood volume ratio in the sample; Another electrode is _ electrode, with (4) although the shirt has been completely reconsidered. In a further embodiment, the conductive layer comprises a five-pole, wherein the second electrode of the conductive layer is connected to the third electrode of the conductive layer to form a reference impurity, and the fourth electrode of the electrical layer is a sample electrode The conductive layer first electrode and the conductive layer fifth electrode are guard electrodes. In another preferred embodiment, the conductive layer comprises five electrodes, wherein the conductive layer first electrode is connected to the conductive layer second electrode to form a common reference electrode, and the third electrode of the conductive layer is an electrode. The fourth electrode and the fifth electrode of the conductive layer are working electrodes. In the electrochemical biosensor test paper provided by the present invention, the four corners of the substrate are obtuse angles to prevent the user from being stabbed or cut by the tip of the substrate during operation. The electrochemical biosensor test paper provided by the present invention further comprises a towel separator covering the conductive layer and a portion of the substrate, and the towel separator is provided with a groove at the reaction end, and is longitudinally and open to the reaction. end. The middle partition is further provided with an opening adjacent to the groove and not communicating with the groove and corresponding to the reaction zone. In the electrochemical biosensor test paper provided by the present invention, the upper partition is provided with an opening for ventilation corresponding to the opening of the middle partition. And the upper partition is provided with a notch at the reaction end. In the preferred embodiment, the notch is semi-circular or semi-elliptical. 201120439 In addition, the electrochemical carbon powder provided in the present invention has a rough section on the outer side of the reaction end. The rough segment is a plurality of straight lines, which are used to increase the roughness of the substrate, prevent the anti-skins f from falling off, and increase the accuracy of the detection. 0 In the electrochemical biosensor test paper provided by the present invention, the method further comprises The adhesive knee layer between the middle plate and the upper partition plate is configured to join the upper partition plate=the middle partition plate and the adhesive layer is provided with a second concave groove corresponding to the groove and the opening of the middle partition plate. The electrochemical biosensor test paper provided by the present invention may further comprise an insulating layer interposed between the conductive layer and the middle partition, wherein the insulating layer is corresponding to the groove and the opening of the middle partition There is a third groove. In summary, the electrochemical biosensor test paper provided by the present invention has the following advantageous effects compared with the prior art and the existing products: - When the electrochemical bio-test paper provided by the present rider is connected with the bio-device _ The device can be used in the paper-recording parameter value, and then the parameter correction step performed by the user simplifies the overall measurement procedure to avoid inaccurate detection due to user omission or operational error. result. Eliminate the cost of manufacturing the lining required to use the wafer card for calibration. Third, the parameter _ component of the remaining wire buckle, listening fresh (four) placed on the front of the substrate 'reduced the complexity of the test paper and the matching biosensor device in the design of the mechanism and manufacturing costs. The use of a variable length electrode to identify the biosensor installed in conjunction with the test strip is used to increase the convenience of use. Please refer to the contents of the present invention and several types of real-times and the details are as follows. In fact, the invention may be implemented as a wire, and the residual frequency is inferred to be limited to the examples mentioned herein. [Embodiment] Figs. 2, 2, and 3 are respectively a perspective exploded view, a stereoscopic view®, and a perspective view of the first embodiment of the present invention. As shown in the first to third figures, the chemical biosensor test paper provided by the present invention comprises a substrate (10) provided with a front surface (and a back surface (10)); and a conductive layer (10) disposed on the front surface of the substrate (10) ( 102) above; - a parameter identification component (10) disposed at the end of the back surface (10) of the substrate (10) and using a correction parameter value of the sacrificial-group; - an upper spacer (10) overlying the conductive layer (10); and - a reaction Zone (10)) is in contact with the conductive layer (10) and is used to carry out the reaction. In addition, the electrochemical bio-test strip provided by the present invention can be further divided into a sensor end (91) and a reaction end (92). In the electrochemical biosensor test paper provided by the present invention, the substrate (1〇) may be a rectangular sheet, preferably having electrical insulation properties. In the preferred embodiment, the four corners of the base plate )0) are obtuse angles (12) to prevent the user from being accidentally stabbed or cut by the tip during operation. The conductive layer (2〇) is coated on the front surface (10) of the substrate, and the conductive layer comprises a conductive silver paste layer (22) and a conductive carbon powder layer (24), the conductive carbon powder layer (24) Covering the conductive silver paste layer (22). The conductive layer (20) comprises at least two electrodes, the three electrodes including at least one working electrode and one reference 12 201120439 electrode. In a preferred embodiment, the conductive layer (20) is longitudinally parallel to the long sides of the substrate (91) and the substrate (10), and is in contact with the biosensor device. Detect changes in electrochemistry. In a preferred embodiment, the electrode of the conductive layer (20) is retracted such that the conductive layer (2) is at the end of the sensor end (91) and the substrate (1) is at the sensor end (91). The ends of the ) are 0.1 to 1 mm apart to avoid the electrochemical biosensor test paper being activated before it is properly inserted into the biosensor device. In a more preferred embodiment, the conductive layer (2〇) is sensed
器化（91)之末端與該基板（1〇)於感測器端（91)之末端相距0.3至 〇. 8公厘；於最佳實施例中，該導電層（2〇)於感測器端（91)之末端 與該基板（10)於感測器端（91)之末端相距〇· 5至〇· 6公厘。 如第一圖所示，本發明所提供之電化學生物感測試紙中，該 上隔板⑽)健蓋於料電層⑽之上，且該上陳⑽設有一 用以通氣之開孔（42)，且該上隔板於反應端（92)設有一缺口 (44)。於較佳實施例中’該缺口（44)呈半圓形或半橢圓形，藉 由缺口（44)的設計’而增加樣品吸人反應區⑽）的面積。由 於缺口（44)增加樣品吸人的面積，因此樣品不但可從侧面平行 試紙的方向吸人反應區⑽）+，並且亦可由上方不同角度吸入 反應區⑽）中’故不但增加使關方便性，並且也可增加樣品 吸入的速度，進而增加試紙的準確性。 本發明所提供之電化學生械職財，槪舰⑽）係 2於基板U0)及部分導電層（2〇)上，其係含有生物活性物 質（如酵素）、酵素輔助因子、安定劑（如高分子聚合物）及緩衝 13 201120439 溶液等’用以與樣本進行反應。 第四圖所不為本發明第一種實施例中導電層之各電極分布情 形。於此實施财’本發騎提供之電化學生物制試紙之該導 電層（20)包含五個電極，分別為一導電層第一電極(2〇2)、一導電 層第二電極(204)、-導電層第三電極⑽6)…導電層第四電極 (208)與-導電層第五電極(209)，且每個導電層電極係由相應之 導電碳粉層電極與導電銀膠層電極所組成，分別為一導電碳粉層 第-電極(242)、-導電碳粉層第二電極⑽）、—導電碳粉層第 三電極(246)、一導電碳粉層第四電極(248)與一導電碳粉層第五 電極(249);以及一導電銀膠層第一電極(222)、一導電銀膠層第 二電極(224)、一導電銀膠層第三電極(226)、一導電銀膠層第四 電極(228)與一導電銀膠層第五電極(229) ，且該五個電極之一端 皆呈縱向且彼此相互平行。此外，該導電銀膠層第二電極(224)具 有一可變長度區(2240)。 於本發明之較佳實施例中，該導電層（2〇)之五個電極中之任 兩個電極相連接形成短路結構。參考第四圖，於更佳實施例中， 該導電層第二電極(204)與該導電層第三電極(206)相連接形成短 路結構，並共同作為一參考電極。 於本發明之較佳實施例中，該導電層（2〇)之五個電極中之任 —個係為一偵測電極，用以偵測一樣本是否已完全進入該反應 區。參考第四圖，於更佳實施例中，該導電層第四電極(2〇8)係為 一偵測電極，用以偵測一樣本是否已完全進入該反應區。 201120439 於本發明之較佳實施例中，該導電層（2〇)之五個電極中之任 一個係為一用以檢測該樣本血糖值之工作電極。於更佳實施例 中，該導電層第五電極(2〇9)係為一用以檢測該樣本血糖值之工作 電極。 於本發明之較佳實施例中，該導電層（2〇)之五個電極中之任 一個係為一用以檢測該樣本血容比之工作電極。於更佳實施例 中’該導電層第-電極(202)係為-用以檢測該樣本血容比之工作 • 電極。 於本發明所提供之電化學生物感測試紙中，該參數辨識元件 (30)係設於該基板（1〇)背面〇〇4)之一端。參考第一圖及第三圖， 於較佳實施例中，該參數辨識元件⑽)係設於該基板⑽之感測 器端（91)背面（1〇4)，且與位於該基板（1〇)正面⑽）之導電層⑽ 形成上下相對位置關係’用以與生物感測器裝置相接觸而加以進 行辨識。 馨 f五圖A至N所示為本發财該參數辨識元件⑽之各種態 樣。本發騎提供之電化學生物❹懷財，該參數辨識元件⑽） 係包含四個以上之不同區塊。於較佳實施例中，該參數辨識元件 (30)包含四個不同之區塊，分別為-第—區塊⑻、—第二區塊 (32)、-第二區塊(33)及-第四區塊(34)。透過各區塊之相互連 通或獨立，本發明中之參數辨識元件(3〇)可形成14種不同之態 樣’且每-態樣係對應於-組特定之校正參數值。於本發明中， 該參數辨識元件⑽各區塊間之連通與獨立係透過雷射侧或刀 15 201120439 具蝕刻加以區隔定義。第五圖A至N中之雙虛線代表各區塊間相 互連通，而雙實線代表各區塊間經過蝕刻而相互獨立。 第五圖A所示為與第一組校正參數值相對應之參數辨識元件 (30A)態樣，其中該參數辨識元件（3〇A)之第一區塊(31)、第二區 塊(32)、第三區塊(33)及第四區塊(34)皆相互連通。 第五圖B所示為與第二組校正參數值相對應之參數辨識元件 (30B)態樣’其中該參數辨識元件（30B)之第一區塊(31)及第二區 塊(32)相互連通且第三區塊(33)及第四區塊(34)相互連通。 第五圖C所示為與第三組校正參數值相對應之參數辨識元件 (30C)態樣’其中該參數辨識元件（30C)之第一區塊(31)及第三區 塊(33)相互連通且第二區塊(32)及第四區塊(34)相互連通。 第五圖D所示為與第四組校正參數值相對應之參數辨識元件 (30D)態樣’其中該參數辨識元件(30D)之第一區塊(31)、第二區 塊(32)、第三區塊(33)及第四區塊(34)均各自獨立不相互連通。 第五圖E所示為與第五組校正參數值相對應之參數辨識元件 (30E)態樣’其中該參數辨識元件（30E)之第一區塊(31)獨立不與 其他區塊相連通且第二區塊(32)、第三區塊(33)及第四區塊(34) 相互連通。 第五圖F所示為與第六組校正參數值相對應之參數辨識元件 (30F)態樣’其中該參數辨識元件（30F)之第三區塊(33)獨立不與 其他區塊相連通且第一區塊(31)、第二區塊(32)及第四區塊(34) 相互連通。 201120439 第五圖G所示為與第七組校正參數值相對應之參數辨識元件 (30G)態樣’其中該參數辨識元件（3〇G)之第四區塊(34)獨立不與 其他區塊相連通且第一區塊(31)、第二區塊(32)及第三區塊(33) 相互連通。 第五圖Η所示為與第八組校正參數值相對應之參數辨識元件 (30Η)態樣，其中該參數辨識元件(3〇Η)之第二區塊(32)獨立不與 其他區塊相連通且第一區塊(31)、第三區塊(33)及第四區塊(34) φ 相互連通。 第五圖1所示為與第九組校正參數值相對應之參數辨識元件 (301)態樣，其中該參數辨識元件(3〇1)之第一區塊(31)與第二區 塊(32)相互連通且第三區塊(33)及第四區塊(34)均各自獨立不相 互連通。 第五圖J所示為與第十組校正參數值相對應之參數辨識元件 (30J)態樣，其中該參數辨識元件(3〇J)之第三區塊(33)與第四區 暑塊(34)相互連通且第一區塊(31)及第二區塊(32)均各自獨立不相 互連通。 第五圖K所示為與第十一組校正參數值相對應之參數辨識元 件（30K)態樣，其中該參數辨識元件（3〇κ)之第一區塊(31)與第三 區塊(33)相互連通且第二區塊(32)及第四區塊(34)均各自獨立不 相互連通。 第五圖L所不為與第十二組校正參數值相對應之參數辨識元 件(30L)態樣，其中該參數辨識元件(3〇L)之第二區塊(32)與第四 17 201120439 區塊(34)相互連通且第一區塊(31)及第三區塊(33)均各自獨立不 相互連通。 第五圖Μ所示為與第十三組校正參數值相對應之參數辨識元 件(30Μ)態樣，其中該參數辨識元件(30Μ)之第二區塊(32)與第三 區塊(33)相互連通且第一區塊(31)及第四區塊(34)均各自獨立不 相互連通。 第五圖Ν所示為與第十四組校正參數值相對應之參數辨識元 件（30Ν)態樣，其中該參數辨識元件(3〇Ν)之第一區塊(31)與第四 區塊(34)相互連通且第二區塊(32)及第三區塊(33)均各自獨立不 相互連通。 於本發明所提供之電化學生物感測試紙中，該參數辨識元件 (30)係由導體喊。在較佳實酬巾’該參數觸元件⑽)係由 碳組成。當該試財具有特定態樣之參數_元件⑽與生物感 、^裝置相連接時，該裝置即能透過辯認該參數辨識元件⑽）中 各區塊之魏麵立獅，自鱗找出無參數觸元件⑽態 樣相對應之一組校正參數值。 第六圖Α所示為本發明第—種電極分布情形，而第六圖 二為本發物導電銀膠層第二電極可變長度區（綱)之各種態 :、八中料電轉層（22)細虛線表示，而該導電碳粉廣⑽ 表7。於本發明之—較佳實施财，料電層第二電極 ，、導第三電極(2⑹相連接且可共_為參考電極用， 、中該導電銀膠層第二電極⑽具有一可變長度區_)，透 201120439 過電阻值之差異來辨認與該電化學生物感測試紙相配合之生物感 測器裝置。於更佳實施例中，該導電銀膠層第二電極可變長度區 (2240)係具有四種不同長度。第六圖b中顯示該導電銀膠層第二 電極可變長度區（2240A)具有全長之長度，並與該導電銀膠層第二 電極(224)之感測器端（91)相連接。第六圖c中顯示該導電銀膠層 第二電極可變長度區（2240B)具有三分之二全長之長度，並與該導 電銀膠層第二電極(224)之感測器端（91)不相連接。第六圖D中顯 豢示該導電銀膠層第二電極可變長度區（224〇c)具有三分之一全長 之長度，並與導電銀膠層第二電極(224)之感測器端（91)不相連 接。第六圖E中顯示該導電銀膠層第二電極可變長度區（224〇1))完 全缺失，並與導電銀膠層第二電極(224)之感測器端（91)不相連 接。 由於導電銀膠層（22)相較於導電碳粉層（24)具有較低之電阻 值，故導電銀膠層第二電極可變長度區（2240)之長度與該電極之 _ 電阻值呈反比關係，亦即導電銀膠層第二電極可變長度區（224〇) 愈長’該電極之餘健愈低。當該電化學生滅測試紙與生物 感測器裝置相連接時，由於該裝置能夠辨識因導電銀膠層第二電 極可變長度區（2240)長度差異所造狀電阻值差異，進而確認該 電化學生械職紙是料與該生物制^裝置相配合之試紙。 第七圖A所示為本發明第二種電極分布情形，其中該導電層 (20A)第-電極⑽2A)與該導電層第二電極⑽4A)相連接形成短 路結構，並共同作為一參考電極；而該導電層第三電極(2_係 201120439 為-細電極；該導電層細電極(腿)係為―用讀測樣本血 糖值之工作電極；該導電層第五電極⑽9A)係為一用以檢測樣本 血容比之工作電極。 另參考第七圖B、C、D及E戶斤示為本發明第二種電極分布情 形中導電銀膠層第二電極可變長度區⑽〇)之各種態樣。其中該 導電銀膠層第二電極(224A)具有-可變長度區⑽Q)。於較佳實 施例争，該導電銀勝層第二電極可變長度區（224〇)係具有四種不 同長度。第七_中顯示該導電轉層第二電極可變長度區（224〇e)馨 具有全長之長度’並與該導電銀膠層第二電極(224A)之感測器端 (91)相連接。第七圖C中顯示該導電銀膠層第二電極可變長度區 (2240F)具有二分之二全長之長度，並與導電銀膠層第二電極 (224A)之感測器端㈤不相連接。第七圖D中顯示該導電銀膠層 第二雜可變長度區（22概)具有三分之一全長之長度，並與該導 電銀膠層第二電極(224A)之感測器端(91)不相連接。第七圖e中 顯不該導電銀膠層第二電極可變長度區（224〇H)完全缺失，並與該籲 導電銀膠層第二電極(224A)之感測器端（91)不相連接。 第八圖為本發明一更佳實施例之立體分解圖。由圖所示，本 發明所提供之電化學生物感測試紙可進一步包含一覆蓋於該導電 層（20)及部分基板(1〇)上之中隔板(5〇)。其中該中隔板(5〇)於反 應端(92)設有一凹槽(52)，呈縱向且開口向該反應端（92)。另外， 該中隔板(50)設有-開口（54) ’該開口（54)係相鄰於該凹槽⑽ 且與該凹槽（52)間不相互連通，並對應於反應區（8〇)。 20 201120439 如第八圖所示，於本發明之較佳實施例中，該導電碳粉層（24) 於反應端（92)外侧設有一粗糙段（240)，較佳地，該粗糙段（240) 可呈一直線或複數段直線。該粗糙段（24〇)可為導電材質，該粗 糙段（240)更佳地由碳粉形成。另外，該粗糙段（240)亦可由 非導電材質製作。該粗縫段（240)係用以增加基板（1〇)之粗糖 度，增加反應區（80)物質貼附強度，防止反應區（8〇)物質脫 落。於本發明之一較佳實施例中，該粗糙段（24〇)位於近反應區 • (8〇)外側。 本發明所提供之電化學生物感測試紙可再進一步包含一介於 該中隔板(50)及該上隔板(40)間之黏膠層（6〇)，用以連接該上隔 板(40)與該中隔板(50)。其中該黏膠層（60)相應於該中隔板(5〇) 之凹槽（52)及開口（54)處設有一第二凹槽（62)。於本發明之較佳 實施例中，該黏膠層（60)係由聚乙烯對苯二曱酸酯(p〇lyethylene Terephthalate’ PET)所組成，並於上下兩面塗佈黏著性材料如水 鲁 膠，用以黏合該上隔板(40)與該中隔板(5〇)。 第九圖為本發明又一更佳實施例之立體分解圖。由圖所示， 本發明所提供之電化學生物感測試紙可再進一步包含一介於該導 電層（20)及該中隔板(50)間之絕緣層（70)，且該絕緣層（7〇)相應 於該中隔板(50)之凹槽(52)及開口（54)處設有一第三凹槽（72)。 雖然前述實施例說明本發明之具體事實，但應瞭解二何可能 的修正及改變均不悖離申請專利範圍中主張之精神及範疇。 21 201120439 【圖式簡單說明】 第一圖係本發明之一較佳實施例之立體分解圖。 第二圖係本發明之—概實關之域上視圖。 第三圖係本發明之—概實施例之域下視圖。 第四圖係本發明之—較佳實施例中導電層之各電極分布。 第五圖A至N係本發明巾參數辨識元件之各種態樣。The end of the device (91) is spaced from the end of the substrate (91) at the end of the sensor end (91) by 0.3 to 8. 8 mm; in the preferred embodiment, the conductive layer (2〇) is sensed. The end of the end (91) is spaced from the end of the substrate (10) at the end of the sensor end (91) by 〇·5 to 〇·6 mm. As shown in the first figure, in the electrochemical biosensor test paper provided by the present invention, the upper partition (10) is covered on the electrical layer (10), and the upper (10) is provided with an opening for ventilation ( 42), and the upper partition is provided with a notch (44) at the reaction end (92). In the preferred embodiment, the indentation (44) is semi-circular or semi-elliptical, increasing the area of the sample inhalation reaction zone (10) by the design of the indentation (44). Since the notch (44) increases the suction area of the sample, the sample can be sucked into the reaction zone (10)+ from the direction of the side parallel test strips, and can also be sucked into the reaction zone (10) from different angles above. And can also increase the speed of sample inhalation, thereby increasing the accuracy of the test strip. The electrochemical bio-management provided by the present invention, the stern (10) is on the substrate U0) and a part of the conductive layer (2 〇), which contains bioactive substances (such as enzymes), enzyme cofactors, stabilizers (such as Polymers and buffers 13 201120439 solutions etc. are used to react with the sample. The fourth figure is not the distribution of the electrodes of the conductive layer in the first embodiment of the present invention. The conductive layer (20) of the electrochemical biotest paper provided by the present invention comprises five electrodes, a conductive layer first electrode (2〇2) and a conductive layer second electrode (204). a conductive layer third electrode (10) 6)... a conductive layer fourth electrode (208) and a conductive layer fifth electrode (209), and each conductive layer electrode is composed of a corresponding conductive carbon powder layer electrode and a conductive silver paste layer electrode The composition is respectively a conductive carbon powder layer first electrode (242), a conductive carbon powder layer second electrode (10), a conductive carbon powder layer third electrode (246), and a conductive carbon powder layer fourth electrode (248 And a conductive carbon powder layer fifth electrode (249); and a conductive silver glue layer first electrode (222), a conductive silver glue layer second electrode (224), a conductive silver glue layer third electrode (226) a fourth electrode (228) of a conductive silver paste layer and a fifth electrode (229) of a conductive silver paste layer, and one of the ends of the five electrodes is longitudinal and parallel to each other. Further, the conductive silver paste second electrode (224) has a variable length region (2240). In a preferred embodiment of the invention, any two of the five electrodes of the conductive layer are connected to form a short circuit structure. Referring to the fourth figure, in a further embodiment, the second electrode (204) of the conductive layer is connected to the third electrode (206) of the conductive layer to form a short-circuit structure and collectively serve as a reference electrode. In a preferred embodiment of the invention, any one of the five electrodes of the conductive layer is a detecting electrode for detecting whether the same portion has completely entered the reaction region. Referring to the fourth figure, in a further embodiment, the fourth electrode (2〇8) of the conductive layer is a detecting electrode for detecting whether the same electrode has completely entered the reaction zone. In a preferred embodiment of the invention, any one of the five electrodes of the conductive layer (2〇) is a working electrode for detecting the blood glucose level of the sample. In a more preferred embodiment, the fifth electrode (2〇9) of the conductive layer is a working electrode for detecting the blood glucose level of the sample. In a preferred embodiment of the invention, any one of the five electrodes of the conductive layer is a working electrode for detecting the blood volume ratio of the sample. In a more preferred embodiment, the conductive layer first electrode (202) is a working electrode for detecting the sample blood volume ratio. In the electrochemical biosensor test paper provided by the present invention, the parameter identification component (30) is disposed at one end of the back surface 4) of the substrate (1). Referring to the first and third figures, in the preferred embodiment, the parameter identification component (10) is disposed on the back surface (1〇4) of the sensor end (91) of the substrate (10), and is located on the substrate (1)导电) The conductive layer (10) of the front side (10) is formed in an up-and-down relative position relationship for identification in contact with the biosensor device. Xin f five figures A to N show the various aspects of the parameter identification component (10). The electrochemical bio-energy provided by the present rider, the parameter identification component (10)) comprises more than four different blocks. In a preferred embodiment, the parameter identification component (30) comprises four different blocks, namely - a first block (8), a second block (32), a second block (33) and - The fourth block (34). Through the interconnection or independence of the blocks, the parameter identification element (3〇) in the present invention can form 14 different states' and each-state pattern corresponds to a group-specific correction parameter value. In the present invention, the communication between the blocks of the parameter identification component (10) and the independent system are defined by etching through the laser side or the knife 15 201120439. The double dashed lines in the fifth diagrams A to N represent the interconnections between the blocks, and the double solid lines represent that the blocks are etched and independent of each other. Figure 5A shows a parameter identification component (30A) corresponding to the first set of correction parameter values, wherein the parameter identification component (3A) is the first block (31) and the second block ( 32) The third block (33) and the fourth block (34) are all connected to each other. Figure 5B shows the parameter identification component (30B) corresponding to the second set of correction parameter values, wherein the first block (31) and the second block (32) of the parameter identification component (30B) The three blocks (33) and the fourth block (34) are connected to each other. Figure 5C shows a parameter identification component (30C) corresponding to the third set of correction parameter values, wherein the first block (31) and the third block (33) of the parameter identification component (30C) The two blocks (32) and the fourth block (34) are connected to each other. The fifth figure D shows the parameter identification component (30D) corresponding to the fourth set of correction parameter values, wherein the first block (31) and the second block (32) of the parameter identification component (30D) The third block (33) and the fourth block (34) are each independently connected to each other. Figure 5E shows a parameter identification component (30E) corresponding to the fifth set of correction parameter values, wherein the first block (31) of the parameter identification component (30E) is independently connected to other blocks. And the second block (32), the third block (33), and the fourth block (34) are connected to each other. The fifth figure F shows the parameter identification component (30F) corresponding to the sixth set of correction parameter values, wherein the third block (33) of the parameter identification component (30F) is independently connected to other blocks. And the first block (31), the second block (32), and the fourth block (34) are connected to each other. 201120439 Figure 5G shows the parameter identification component (30G) corresponding to the seventh set of correction parameter values. The fourth block (34) of the parameter identification component (3〇G) is independent of other zones. The blocks are in communication and the first block (31), the second block (32), and the third block (33) are in communication with each other. The fifth figure Η shows the parameter identification component (30Η) corresponding to the eighth set of correction parameter values, wherein the second block (32) of the parameter identification component (3〇Η) is independent of other blocks. The first block (31), the third block (33), and the fourth block (34) φ are connected to each other. The fifth figure 1 shows a parameter identification component (301) corresponding to the ninth set of correction parameter values, wherein the parameter identification component (3〇1) is the first block (31) and the second block ( 32) are interconnected and each of the third block (33) and the fourth block (34) are independently connected to each other. The fifth figure J shows the parameter identification component (30J) corresponding to the tenth set of correction parameter values, wherein the third block (33) of the parameter identification component (3〇J) and the fourth zone summer block (34) are interconnected and each of the first block (31) and the second block (32) are independently connected to each other. The fifth figure K shows a parameter identification component (30K) corresponding to the eleventh set of correction parameter values, wherein the parameter identification component (3〇κ) of the first block (31) and the third block (33) are interconnected and each of the second block (32) and the fourth block (34) are independently connected to each other. The fifth figure L is not the parameter identification component (30L) corresponding to the twelfth group of correction parameter values, wherein the parameter identification component (3〇L) of the second block (32) and the fourth 17 201120439 The blocks (34) are connected to each other and the first block (31) and the third block (33) are each independently not connected to each other. The fifth figure Μ shows the parameter identification component (30Μ) corresponding to the thirteenth set of correction parameter values, wherein the parameter identification component (30Μ) of the second block (32) and the third block (33) The two blocks (31) and the fourth block (34) are connected to each other independently of each other. The fifth figure Ν shows the parameter identification component (30Ν) corresponding to the fourteenth set of correction parameter values, wherein the first block (31) and the fourth block of the parameter identification component (3〇Ν) (34) are interconnected and each of the second block (32) and the third block (33) are independently connected to each other. In the electrochemical biosensor test paper provided by the present invention, the parameter identification element (30) is shouted by a conductor. In the preferred embodiment, the parameter touch element (10) is composed of carbon. When the test has a specific parameter _ component (10) connected to the biological sense device, the device can identify the Wei lion lion in each block in the parameter identification component (10). The parameterless contact element (10) aspect corresponds to a set of correction parameter values. The sixth figure 为本 shows the first electrode distribution of the present invention, and the sixth figure 2 shows the various states of the second electrode variable length region (the outline) of the conductive silver glue layer of the present invention: 22) The thin dotted line indicates that the conductive carbon powder is wide (10) Table 7. In the preferred embodiment of the present invention, the second electrode of the electrical layer, the third electrode (2(6) is connected and can be used together as a reference electrode, and the second electrode (10) of the conductive silver paste layer has a variable Length zone _), through the difference of the resistance value of 201120439 to identify the biosensor device matched with the electrochemical biosensor test paper. In a more preferred embodiment, the conductive silver paste layer second electrode variable length region (2240) has four different lengths. The second electrode variable length region (2240A) of the conductive silver paste layer has a full length and is connected to the sensor end (91) of the second electrode (224) of the conductive silver paste layer. The sixth electrode c shows that the second electrode variable length region (2240B) of the conductive silver paste layer has a length of two-thirds of the total length and is opposite to the sensor end of the second electrode (224) of the conductive silver paste layer. ) not connected. In the sixth figure D, the second electrode variable length region (224〇c) of the conductive silver paste layer has a length of one third of the total length, and the sensor of the second electrode (224) of the conductive silver paste layer The ends (91) are not connected. In the sixth figure E, the second electrode variable length region (224〇1) of the conductive silver paste layer is completely missing, and is not connected to the sensor end (91) of the second electrode (224) of the conductive silver paste layer. . Since the conductive silver paste layer (22) has a lower resistance value than the conductive carbon powder layer (24), the length of the second electrode variable length region (2240) of the conductive silver paste layer and the _ resistance value of the electrode are The inverse relationship, that is, the longer the variable length region (224〇) of the second electrode of the conductive silver paste layer, the lower the residual health of the electrode. When the electrochemical biocidal test paper is connected to the biosensor device, the device can recognize the difference in the resistance value caused by the difference in the length of the second electrode variable length region (2240) of the conductive silver paste layer, thereby confirming the electrochemicalization. The student's paper is a test paper that is matched with the biological device. 7 is a second electrode distribution of the present invention, wherein the conductive layer (20A) first electrode (10) 2A) is connected to the conductive layer second electrode (10) 4A) to form a short-circuit structure, and together serve as a reference electrode; The third electrode of the conductive layer (2_ is 201120439 is a thin electrode; the thin electrode (leg) of the conductive layer is a working electrode for reading blood glucose value of the sample; the fifth electrode (10) 9A of the conductive layer is used for one purpose. To test the sample blood volume ratio of the working electrode. Referring to Figures 7B, C, D and E, respectively, various aspects of the second electrode variable length region (10) of the conductive silver paste layer in the second electrode distribution of the present invention are shown. The second electrode (224A) of the conductive silver paste layer has a variable length region (10) Q). In a preferred embodiment, the conductive silver layer second electrode variable length region (224 〇) has four different lengths. In the seventh_the second conductive variable length region (224〇e) of the conductive layer, the length of the full length is shown and connected to the sensor end (91) of the second electrode (224A) of the conductive silver paste layer. . In the seventh figure C, the second electrode variable length region (2240F) of the conductive silver paste layer has a length of two-half of the total length and is different from the sensor end (f) of the second electrode (224A) of the conductive silver paste layer. connection. In the seventh figure D, the second impurity variable length region (22) of the conductive silver paste layer has a length of one third of the total length and is opposite to the sensor end of the second electrode (224A) of the conductive silver paste layer ( 91) Not connected. In the seventh figure e, the second electrode variable length region (224〇H) of the conductive silver paste layer is completely missing, and the sensor end (91) of the second electrode (224A) of the conductive silver paste layer is not Connected. Figure 8 is a perspective exploded view of a preferred embodiment of the present invention. As shown in the figure, the electrochemical biosensor test paper provided by the present invention may further comprise a spacer (5〇) covering the conductive layer (20) and a portion of the substrate (1). The middle partition (5 〇) is provided with a groove (52) at the reaction end (92), which is longitudinal and opens toward the reaction end (92). In addition, the middle partition (50) is provided with an opening (54) 'the opening (54) is adjacent to the groove (10) and does not communicate with the groove (52), and corresponds to the reaction zone (8) 〇). 20 201120439 As shown in the eighth embodiment, in the preferred embodiment of the present invention, the conductive carbon powder layer (24) is provided with a rough section (240) outside the reaction end (92), preferably, the rough section ( 240) Can be in a straight line or a complex line. The roughened section (24 turns) may be a conductive material, and the roughened section (240) is more preferably formed of carbon powder. Alternatively, the roughened section (240) can be made of a non-conductive material. The thick slit section (240) is used to increase the coarseness of the substrate (1〇), increase the adhesion strength of the reaction zone (80), and prevent the reaction zone (8〇) from falling off. In a preferred embodiment of the invention, the rough section (24〇) is located outside the near reaction zone (8〇). The electrochemical biosensor test paper provided by the present invention may further comprise an adhesive layer (6〇) interposed between the middle partition (50) and the upper partition (40) for connecting the upper partition ( 40) with the middle partition (50). The adhesive layer (60) is provided with a second recess (62) corresponding to the recess (52) and the opening (54) of the middle partition (5〇). In a preferred embodiment of the present invention, the adhesive layer (60) is composed of polyethylene terephthalate (PET), and is coated with an adhesive material such as water gelatin on both upper and lower sides. For bonding the upper partition (40) and the middle partition (5〇). Figure 9 is a perspective exploded view of still another preferred embodiment of the present invention. As shown in the figure, the electrochemical biosensor test paper provided by the present invention may further comprise an insulating layer (70) interposed between the conductive layer (20) and the intermediate spacer (50), and the insulating layer (7) 〇) A third groove (72) is provided corresponding to the groove (52) and the opening (54) of the middle partition (50). While the foregoing embodiments illustrate the specific aspects of the invention, it should be understood that the modifications and changes may be made without departing from the spirit and scope of the claims. 21 201120439 [Brief Description of the Drawings] The first drawing is an exploded perspective view of a preferred embodiment of the present invention. The second figure is a top view of the domain of the present invention. The third drawing is a lower view of the domain of the present invention. The fourth figure is the distribution of the electrodes of the conductive layer in the preferred embodiment of the invention. Fifth panels A through N are various aspects of the towel parameter identification component of the present invention.
第^圖A至E係本發明第一種電極分布情形及導電銀膠層第二電 極可變長度區之各種態樣。 I 第七圖A至E係本發明第二種電極分布情形及導電銀膠層第二電 極可變長度區之各種態樣。 第八圖係本發明之—更佳實侧之靖分解圖。 第九圖係本發日狀又—更佳實施例之讀分解圖。 【主要元件符號說明】 10 :基板 _ 102 :基板正面 104 :基板背面 12 :鈍角 20、20A :導電層 202、202A ·導電層第一電極 204、204A :導電層第二電極 22 201120439 206、206A :導電層第三電極 208、 208A :導電層第四電極 209、 209A :導電層第五電極 22 :導電銀膠層 222、222A :導電銀膠層第一電極 224、224A :導電銀膠層第二電極 2240、2240A、2240B、2240C、2240D、2240E、2240F、2240G、 • 2240H :導電銀膠層第二電極可變長度區 226 :導電銀膠層第三電極 228 :導電銀膠層第四電極 229 :導電銀膠層第五電極 24 :導電碳粉層 240 :粗糙段 242 :導電碳粉層第一電極 • 244 :導電碳粉層第二電極 246 :導電碳粉層第三電極 248 :導電碳粉層第四電極 249 :導電碳粉層第五電極 30 :參數辨識元件 30A :與第一組校正參數值相對應之參數辨識元件 30B :與第二組校正參數值相對應之參數辨識元件 30C :與第三組校正參數值相對應之參數辨識元件 23 201120439 :.四組校正參數值相對應之參數辨識元件 識元件 Qnr .&咕 -^ 識元件 .·、七組校正參數值相對應之參數辨識元件 —邳對應之參數辨 施與第五組校正參數值相對 -·:與第六組校正參數值相對應之參識讀 〆项兀/J牛Figs. A to E show various aspects of the electrode distribution of the present invention and the second electrode variable length region of the conductive silver paste layer. I Seventh A to E are various aspects of the second electrode distribution of the present invention and the second electrode variable length region of the conductive silver paste layer. The eighth figure is an exploded view of the better side of the present invention. The ninth figure is a reading exploded view of the present invention. [Main component symbol description] 10: Substrate_102: Substrate front side 104: Substrate back surface 12: Obtuse angle 20, 20A: Conductive layer 202, 202A · Conductive layer first electrode 204, 204A: Conductive layer second electrode 22 201120439 206, 206A : Conductive layer third electrode 208, 208A: conductive layer fourth electrode 209, 209A: conductive layer fifth electrode 22: conductive silver adhesive layer 222, 222A: conductive silver adhesive layer first electrode 224, 224A: conductive silver adhesive layer Two electrodes 2240, 2240A, 2240B, 2240C, 2240D, 2240E, 2240F, 2240G, • 2240H: conductive silver glue layer second electrode variable length region 226: conductive silver glue layer third electrode 228: conductive silver glue layer fourth electrode 229: conductive silver paste layer fifth electrode 24: conductive carbon powder layer 240: rough section 242: conductive carbon powder layer first electrode • 244: conductive carbon powder layer second electrode 246: conductive carbon powder layer third electrode 248: conductive Carbon powder layer fourth electrode 249: conductive carbon powder layer fifth electrode 30: parameter identification element 30A: parameter identification element 30B corresponding to the first group of correction parameter values: parameter identification element corresponding to the second group of correction parameter values 30C: with the third set of correction parameter values Corresponding parameter identification component 23 201120439 :. Four sets of correction parameter values corresponding to the parameter identification component identification component Qnr .&咕-^ identification component.·, seven sets of correction parameter values corresponding to the parameter identification component-邳 corresponding parameter The identification is relative to the fifth set of correction parameter values -·: the reading corresponding to the sixth set of correction parameter values / J cattle
30Η :與第讀校正參數值姆應之參數辨識元件 301 :與第九組校正參數值相對應之參數辨識元件 3〇J :與第十組校正參數值相對應之參數辨識元件 30Κ ··與第十—組校正參數值械應之參數辨識元利 30L :與第十二組校正參數值相對應之參數辨識元列 30Μ :與第十三組校正參數值相對應之參數辨識元利 31 33 40 44 52 第一區塊 32:第二區塊 第三區塊 34 :第四區塊 上隔板 42:開孔 缺口 50:中隔板 凹槽 54 :開口 黏膠層 62 :第二凹槽 絕緣層 72 :第三凹槽 反應區 91 :感測器端30Η: Parameter identification element 301 corresponding to the first reading correction parameter value: Parameter identification element corresponding to the ninth group of correction parameter values: 参数J: Parameter identification element corresponding to the tenth group of correction parameter values Κ·· The tenth-group calibration parameter value parameter identification element element 30L: the parameter identification element column corresponding to the twelfth group correction parameter value 30Μ: parameter identification corresponding to the thirteenth group correction parameter value Yuanli 31 33 40 44 52 first block 32: second block third block 34: fourth block upper partition 42: opening notch 50: middle partition groove 54: open adhesive layer 62: second groove insulating layer 72: third groove reaction zone 91: sensor end
92 :反應端 2492: reaction end 24