ΐΥϋ«ϋ474 五、新型說明： 【新型所屬之技術領域】 本創作係關於一種電化學生物感測試紙，尤指一種於基板背 面一端設有一參數辨識元件而能免去使用者進行參數校正步驟之 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，現在大多走向居家測試的方向。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 員及居家護理使用’不會有污染的情形發生，並且配合適當的生 物感測器裝置，即可測量出正確的測量數值。 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餅針普遍·的床邊 檢測（Point of care test，p〇CT)醫療器材之一。根據台灣糖尿 病學會的崎報告_ ’目前㈣錄_分析原理，主要是利 用電化予(Amperometric electrochemistry)原理進行測試；當血 液中葡萄糖與電化學生物_試紙上之酵素產生電化學反應後， 借由介質電子的釋出’透過血糖機將電流變化轉換為血糖濃度數 值。 S用之電化學生物感測試紙具有—基板、—導電層、一反應 區及上隔板’在該基板上形成導電層，該導電層包含二條分離 M380474 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—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1：極料至導電層另-端之陰極接酿陽極接頭， 籲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化的比 production)之方式製造’因此製造過程中的各項咖將造成每批 試紙間的差異性，例如工作電極與參考電極的體積、反應區内的 酵素量等，皆會影響檢測導致測量結果不準確。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，以確認檢驗分析值的一致性。血糖機内參數的校正作用即 在於讀認試紙;f會因為製造減*同，而林同的分析結果。 。目前市售錄_參數校正方法主要有“蚊法、試紙編 號核對法等。以晶片設定法為例，每盒血糖試紙在㈣使用前， 校正血糖機内之參數，然而病患或實施測 篁的家屬卻時常忘記這個校正動作，導致測量得出之血糖值不甚 準確而不自知。吳國創作專利公開號第2__13號所提供之 5 M380474 -種可個參數校正試紙進行參數校正之生物_錄置，其參 數校正方式便與此近似。而美國創作專利第7,514，議號，侧 於-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 ^其於生物❹m裝置_數組校轉數值，額者於進行測 置前須先選定與雜試紙她合之參練，其參紐正方式係屬 於試紙編號核對法。 如先前技術中所提及，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，祕檢測程序上的 繁瑣’且細者-旦疏漏或未正確執行該校正步驟，則無法得到 =確之檢聽果’不僅浪費時間與資源，更對病患之生活與健康 s理造成貞面影響。依據糖尿錄教學會贏年触統計顯示， 32. 9%的病患錯誤使用血_，包括制前忘記校正，導致測量不 準確’影響錢控制。前述缺失對使时造狀不便，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 仍此維持測量結果之準確性，乃為相關業者亟待改進之處。 【新型内容】 名詞定義 生物感測器裝置 係指與本創作所提供之電化學生物感測試紙相配合以檢測一 篆本中特疋物質濃度之裝置’如血糖儀、細醇儀、尿酸儀等。 感測器端 6 係指本創作所提供之電化學生物感測試紙於使用時與生物感 測器裝置相接觸之一端。 反應端 一係指本創作所提供之電化學生物感測試紙於使用時與樣本進 行％之端’通常即反應區所在之一端，並相對於感測器端。 如先前技術中所提及，為了省去使用者在測量前的校正步 驟’但仍能轉測4結果之準雜，糊觸提供—種電化學生 物感測試紙’其巾包含—設於基板背面H數職元件，使 該試紙與生物感·裝置連接時即可自動選擇姆應於該批試紙 之-組校正參触’ _省去由個魏行的參紐正步驟，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。 本創作之技術手段在於提供-種電化學生物感測試紙，其係 包含-基板，係設有-正面及-背面；—導電層，設於該基板正 面之上；一參數辨識元件，設於該基板背面之一端且用以對應一 組特定之校正參數值；一上隔板，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。 於本創作之較佳實施例中，本創作所提供之電化學生物感測 試紙中之參數辨識元件包含四個以上之不同區塊，透過各區塊之 相互連通或獨立，該參數辨識元件可形成複數種不同之態樣，且 母一態樣係對應於一組特定之校正參數值，故當具有特定來數辨 M380474 識元件態樣之試紙與一生物感測器裝置連接時，該裝置便能自動 選擇與該批試紙相對應之一組校正參數值。 於更佳實施财’本解所提供之電化學生物_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 四區塊等四魏塊。藉由該四麵塊之相互連通或獨立，本創作 中之參數辨識元件可形成14種不同之態樣，且每一態樣係對應於 一組特定之校正參數值。 本創作所提供之電鱗生械觀財之錄_元件係可 由導體所組成；於較佳實施例中，該參數辨識元件係由碳所組成， 且參數辨識元件各區額之連通觸立係_雷祕刻或刀錢 刻加以區岐A。於難實_+，該絲觸元㈣設於基板 之感測器端背面。 於本創作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_触電鱗生械測觀她 置》藉由改變電極之長度，可調整該電極之電_，t=j ^物感測試紙與-生物感測器裝置相連鱗，透過電阻值之測 量，可肋觸她合之生減測邱^於較佳實施例中，該 可變成長賴具有_不度，故可辨認_獨之生物感列 器裝置。此外，於更佳實施财，具有財變長度區之電極係作 為一參考電極。 於本創作所提供之電化學生物感測試紙中，該導電層包括一 8 M380474 導電銀謬層及i電碳粉層，且該導電碳粉層覆蓋於該導電轉 層之上。每辦電層電極係由域之導電碳粉層電極與導電銀膠 層·所組成。例如，導電層第一電極係由導電銀踢層第一電極 與導電碳騎第-雜所域，導第二雜係由導電銀膠層 第二電極與導電碳崎第二雜所喊，依此類推。 於本創作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’㈣免電化學缝_試紙在正钮插入生物 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，分別為一導電 層第-電極…導電層第二電極、—導電層第三電極、—導電層 第四电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一可變長度 區’用以辨認與該電化學生物感測試紙相配合之生物感測器裝 置。且該導電層之五個電極中的任兩個電極相連接形成短路結 構，該短路結構可啟動相符合而用以偵測試紙檢測結果 的生物感測器裝置。於更佳實施射，該導電層之第二電極與 第二電極相連接形成短路結構，並共同做為一參考電極。 於另-更佳實施例中，該導電層第一電極與該導電層第二電 極相連接形成短路結構，並共同做為一參考電極。 於本創作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—個電極為參考電極，且其中至少一個電 9 極為工作電極。於較佳實 兩個電極相連接形成_共用之參考電7層另包兩合=電極，其中 極’分別用以檢測樣本t之血糖值與血容比 電極，肋_縣是奸完全以反顧 測 該導電層包含五個電極，其_第二電極：： 電極相連接形成H參考電極， 4導電層第二 極… 層細電極為偵測電 該導電層第—電極與鱗第五電極為工作電極。 ―於另一更佳實施财，料騎包含五個電極，其中該導電 電極與該導電層第二電極相連接形成—共用之參考電極， 電層第二電極為_電極’而該導電層第四電極與第五電極 為工作電極。 於本創作所提供之魏學生物制顺巾，該基板之四個角 係為鈍角，_免義者_作财龍基板线傷或割傷。 於本創作所提供之電化學生物❹m财，進—步包含一覆蓋 於導電層及β刀基板上之中隔板，且該中隔板於反應端設有一凹 槽，呈縱向且開π向該反應端。該中隔板另設有—開口，該開口 係相鄰於該凹槽且與該凹槽間不相互連通，並對胁該反應區。 於本創作所提供之電化學錄朗觀巾，社隔板相應於 中隔板之開Π處対—用以通氣之開孔。雌上隔板於反應端設 有-缺Π，_佳實施财，該細科_辭麵形。 另外’於糊鑛提供之電辨生物_試紙中，該導電碳 粉層於反應端糊設有-祕段。雜赌為減段直線，其係 用以增加基板的粗輪度，防止反應區物質脫^，增加檢測的準確 性。 於本創作所提供之電化學生物感測試紙中，進 一入 於該中隔板及該上_之_,魏接合該上隔板及;= 板，且該轉層減於該巾隔板之凹槽及•處設有—第二凹 槽。於本齡所提供之電化學生物制試紙中，可再進—步包含 ’丨於該導電層及該巾隔板間之絕緣層，其巾該絕緣層相應於該 中隔板之凹槽及開口處設有一第三凹槽。 〜、 综上所述，本創作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： -、本創作所提供之電化學生物感測試紙與生物感測器裝置連接 時即可使該裝置自動麵補餘雜試紙之-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，避免因使用者疏漏或操作錯誤而導致不準蜂之檢測結 果。 一、免去需使用晶片卡進行校正所需之額外製造成本。 ―、將參數辨識70件設於基板之背面，避免與導電層共置於基板 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。 四、透過可變長度之電極以辨認與賴紙她合之生物感測器裝 置’增加使用上之方便性。 本創作内容及若干具體實施例請參考附圖且詳述如下。事實 M380474 上，本創作可能以不同的形式來實施’且不應該被推斷為僅限於 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創作第_種實施例之 立體分解®、立體上棚及立體下棚。如第—圖至第三圖所示， 本創作所提供之電化學生物_試紙包含—基板⑽，係設有一 正面⑽)及-背面⑽）；—導電層⑽，設於該基板⑽正面 (102)之上；一參數辨識元件（3〇)，設於該基板（1〇)背面（1〇4)之 -端且用崎應-組特定之校正參數值；—上隔板⑽，覆蓋於 該導電層（20)之上；以及一反應區（8〇)，與該導電層（2〇)接觸且 用以進行反應。此外，本創作所提供之電化學生物感測試紙可進 一步區分為一感測器端（91)及一反應端（92)。 本創作所提供之電化學生物感測試紙令，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（10)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（20)塗佈於基板（10)正面（1〇2)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（2〇) 至夕、包3二條電極，該三條電極中至少包括一工作電極及一參考 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 12 M380474 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 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 器裝置刖便啟動該裝置。於更佳實施例中，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0.3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，本創作所提供之電化學生物感測試紙中，該 上隔板⑽係覆蓋於料電層⑽之上，且該上隔板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)。於較佳實施例巾’該缺口（44)呈半圓形或半賴形，藉 由缺口（44)的设計，而增加樣品吸入反應區⑽）的面積。由 於缺口（44)增加樣品吸入的面積，因此樣品不但可從側面平行 •試紙的方向吸入反應區（80)中，並且亦可由上方不同角度吸入 反應區⑽中，故不但增加使用的方便性，並且也可增加樣品 吸入的速度’進而增加試紙的準確性。 本創作所提供之電化學生物❹懷财，飯顧⑽）係 覆蓋於基板U0)及部分導電層（2〇)上，其係含有生物活性物 質（如酵素）、酵素辅助因子、安定劑（如高分子聚合物）及緩衝 溶液等’用以與樣本進行反應。 第四圖所示為本創作第一種實施例中導電層之各電極分布情 13 M380474 形。於此實施例中，本創作所提供之電化學生物感測試紙之該導 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)、一導電層第三電極(206)、一導電層第四電極 (208)與一導電層第五電極(2〇9)，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 第一電極(242)、一導電碳粉層第二電極(244)、一導電碳粉層第 二電極(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—可變長度區（2240)。 於本創作之較佳實施例中，該導電層（20)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(2〇4)與該導電層第三電極(2〇6)相連接形成短 路結構，並共同作為一參考電極。 於本創作之較佳實施例中，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(208)係為 偵測電極，用以價測一樣本是否已完全進入該反應區。 於本創作之較佳實施例中，該導電層（20)之五個電極中之任 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 M380474 中該V電層第五電極(209)係為-用以檢測該樣本血糖值之工作 電極β 於本創作之較佳實施例中，該導電層（20)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’該導電層第一電極(202)係為一用以檢測該樣本血容比之工作 電極。 於本創作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(10)背面（104)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（104)，且與位於該基板(10)正面（1〇2)之導電層⑽ 形成上下相對位置肋與生物感·裝置相接觸而加以進 行辨識。 第五圖Α至Ν所示為本創作中該參數辨識元件(3〇)之各種態 樣。本創作所提供之電化學生物感測試紙中，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，分別為一第一區塊(31)、一第二區塊 (32)、一第三區塊(33)及一第四區塊(34)。透過各區塊之相互連 通或獨立，本創作中之參數辨識元件⑽可形成14種不同之態 樣，且每一態樣係對應於一組特定之校正參數值。於本創作中， 該參數辨識元件（30)各區塊間之連通與獨立係透過雷射蝕刻或刀 具侧加以區隔定義。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钱刻而相互獨立。 15 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（3〇B)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⑽G)之第—區塊⑶）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-區塊(31)、第二區 塊(32)、第二區塊(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-區塊(31)獨立不與 其他區塊相連通且第二區塊⑽、第三區塊⑶)及第四區塊⑽ 相互連通。 第五圖F所不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⑽F)之第三區塊⑽獨立不與 其他區塊相連通且第—區塊⑻、第二區塊⑽及第四區塊⑽ 相互連通。 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 (觸祕’其中該參數辨識元件(30G)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(30Η)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) 相互連通。 第五圖I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 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（30K)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所示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 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。 17 M380474 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(3〇Μ)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。 於本創作所提供之電化學生物感測試紙中，該參數辨識元件 (30)係由導體組成。在較佳實施例中，該參數辨識元件(3〇)係由 碳組成。當該試紙中具有特定態樣之參數辨識元件(3〇)與生物感 測器裝置相連接時，該裝置即能透過辯認該參數辨識元件(3〇)中 各區塊之連通或獨立情形，自動尋找出與該參數辨識元件(3〇)態 樣相對應之一組校正參數值。 第✓、圖Α所示為本創作第一種電極分布情形，而第六圖β至ε 係為本創作該導電銀膠層第二電極可變長度區（2240)之各種態 樣其中該導電銀膠層（22)係以虛線表示，而該導電碳粉層（24) 係以實線表示。於本創作之一較佳實施例中，該導電層第二電極 (204)與導電層第三電極(2〇6)相連接且可共同做為參考電極用， 且其中該導電銀膠層第二電極(224)具有一可變長度區（224〇)，透 過電阻值之差異來辨認與該電化學㈣感職紙相配合之生物感 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 M380474 (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（2歷)具有全長之長度，並無導驗膠層第二 電極(224)之感測器端⑽相連接。第六圖c中顯示該導電銀膠層 第二電極可縣度區（22棚)具有三分之二全長之長度，並與該導 電銀膠屬第二電極(224)之感測器端（91)不相連接。第六圖D中顯 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⑼）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（22柳)完 全缺失’並與導電銀膠層第二電極(224)之感測器端⑽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（224G)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（測） 愈長，該雜之電阻健愈低。當該電化學生物❹域紙與生物 >感湘裝置相連接時’由於魏置能夠辨翻導電銀縣第二電 極可變長度11(2240)長度差異所造成之電阻值差異 ，進而確認該 電化學生物_試紙是否為與該生_ 裝置她合之試紙。 第七圖A所7F為本創作第二種電極分布情形，其中該導電層 (20A)第-電極(2G2A)與該導電層第二電極(腿)相連接形成短 路結構，並共同作為-參考電極；而該導電層第三電極(腿)係 為-細電極，·該導電層第四電極(2〇8A)係為一用以檢測樣本血 糖值之工作電極’該導電層第五電極(2隱)係為一用以檢測樣本 19 1V1J0U4/4 血容比之工作電極。 ，另參考第，B、C、D及E所示為本創作第二種電極分布情 形中導電轉衫二電極可縣度區(2_之各_樣。其中該 導電銀膠層第二電極(224A)具有—可變長度區(224Q)。於較佳實 施例中’該導電轉層第二電極可變長度區（2_係具有四種不 同長度弟七圖B中顯示該導電銀膠層帛二電極可變長度區⑵概) 八有王長之長度’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中顯示該導電銀縣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)之制n端(91)不相連接。第七圖D巾顯示該導電銀膠層 第二電極可變長度區（2240G)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£中 顯示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 導電銀膠層第二電極(224A)之感測器端（91)不相連接。 第八圖為本創作一更佳實施例之立體分解圖。由圖所示，本 創作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)設有一開口（54) ’該開口（54)係相鄰於該凹槽(52) 且與該凹槽（52)間不相互連通，並對應於反應區（8〇)。 如第八圖所示’於本創作之較佳實施例中，該導電碳粉層（24) 於反應端（92)外側設有一粗糙段（240)，較佳地，該粗縫段（240) 20 M380474 可呈一直線或複數段直線。該粗糙段（240)可為導電材質，該粗 链段（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。該粗糙段（240)係用以增加基板（1〇)之粗糙 度，增加反應區（80)物質貼附強度，防止反應區（8〇)物質脫 落。於本創作之一較佳實施例中，該粗糙段（24〇)位於近反應區 (80)外侧。 - 本創作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(5〇)及該上隔板(40)間之黏膠層（60)，用以連接該上隔 板(40)與該中隔板(50)。其中該黏膠層（6〇)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)。於本創作之較佳 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 膠，用以黏合該上隔板(40)與該中隔板(5〇)。 第九圖為本創作又一更佳實施例之立體分解圖。由圖所示， ·"本創作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（7〇)，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創作之具體事實，但麟解任何可能 的修正及改變均不幢離申請專利範圍中主張之精神及範齊。 【圖式簡單說明】 第一圖係本創作之一較佳實施例之立體分解圖。 第二圖係本創作之一較佳實施例之立體上視圖。 弟二圖係本創作之一較佳實施例之立體下視圖。 弟四圖係本創作之一較佳實施例中導電層之各電極分布。 第五圖A至N係本創作中參數辨識元件之各種態樣。 第六圖A至E係本創作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。 第七圖A至E係本創作第二種電極分布跡及導電銀膠層第二電 極可變長度區之各種態樣。 第八圖係本解之-更佳實施例之謂分解圖。 第九圖係本創作之又-更佳實施例之立體分解圖。 【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 M380474 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、 φ 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 M380474 30D :與第四組校正參數值相對應之參數辨識元件 30E :與第五組校正參數值相對應之參數辨識元件 30F :與第六組校正參數值相對應之參數辨識元件 30G :與第七組校正參數值相對應之參數辨識元件 30H :與第八組校正參數值相對應之參數辨識元件 301 :與第九組校正參數值相對應之參數辨識元件 30J :與第十組校正參數值相對應之參數辨識元件 30K :與第十一組校正參數值相對應之參數辨識元件 30L :與第十二組校正參數值相對應之參數辨識元件 30M :與第十三組校正參數值相對應之參數辨識元件 30N :與第十四組校正參數值相對應之參數辨識元件 31 :第一區塊 32:第二區塊 33 :第三區塊 34 :第四區塊 40 :上隔板 42 :開孔 50:中隔板 54 :開口 62 :第二凹槽 72 :第三凹槽 91 :感測器端 44 :缺口 52 :凹槽 60:黏膠層 70 :絕緣層 80 :反應區 92 :反應端 24ΐΥϋ«ϋ474 V. New description: [New technical field] This creation is about an electrochemical biosensor test paper, especially one that has a parameter identification component at the back end of the substrate to eliminate the user's parameter correction steps. Electrochemical biosensor test paper. [Prior Art] Due to advances in technology, many of the tests that had to be tested in hospitals in the past have now mostly moved toward home testing. At present, there are many biosensor test papers that can be discarded after one use and used for home operation. It is suitable for non-professionals and home care use. It will not cause pollution, and it is equipped with appropriate biosensor devices. , you can measure the correct measurement value. 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 clinical equipment and the point of care test (p〇CT) medical equipment. According to the Taiwan Diabetes Association's Saki report _ 'current (four) record _ analysis principle, mainly using the principle of electrochemical (Amperometric electrochemistry) test; when the blood glucose and electrochemical bio-test paper enzymes electrochemical reaction, by The release of medium electrons 'converts the current change into the blood glucose concentration value through the blood glucose machine. The electrochemical biosensing test paper for S has a substrate, a conductive layer, a reaction zone and an upper separator, and a conductive layer is formed on the substrate, the conductive layer comprising two anode portions and a cathode which are separated from each other and are not in contact with each other. Part of 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 cathode of the conductive layer forms 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 covered on the reaction zone - the upper separator. When the sample is inhaled - the sample will react with the reaction zone material and produce an electrochemical change, and the electrode is connected to the cathode of the other end of the conductive layer. The biosensor device connects and receives the signal, and after calculation, converts the signal into a concentration of the analyte to be displayed on a display. However, since electrochemical biosensor test papers are currently manufactured in a mass-produced manner than production, the coffee in the manufacturing process will cause differences between each batch of test papers, such as the volume of the working electrode and the reference electrode, The amount of enzyme in the reaction zone, etc., will affect the detection and result in inaccurate measurement results. Therefore, the blood glucose meter test strips are shipped from the factory. The manufacturer will set a specific set of calibration parameters according to each batch of products to confirm the consistency of the test analysis values. The correction function of the parameters in the blood glucose machine is to read the test paper; f will be the same as the result of the analysis. . At present, the market calibration method mainly includes “mosquito method, test paper number verification method, etc. Taking the wafer setting method as an example, each box of blood glucose test paper is used to correct the parameters in the blood glucose meter before use, but the patient or the tester is performing the test. The family members often forget this corrective action, which leads to the measurement of the blood sugar value is not accurate and does not know. Wu Guo created the patent publication No. 2__13 provided by the 5 M380474 - a parameter correction test paper for parameter correction of the _ For the recording, the parameter correction method is similar to this. The US patent No. 7,514, the negotiation number, the side-by-side built-in parameter password can also be embedded with the parameter password, and the smart biosensor is installed in the bio-M device. _ Array calibrated value, the amount must be selected before the measurement and the test paper, she is involved in the test, the positive method is the test paper number verification method. As mentioned in the prior art, regardless of the use of blood glucose machine A parameter correction method 'is required to additionally increase the user's operation steps, the cumbersomeness of the secret detection procedure, and the fineness - if the omission is omitted or the correction step is not correctly performed, then no Obtaining = correcting the results of the hearing is not only a waste of time and resources, but also has a negative impact on the life and health of the patient. According to the statistics of the diabetes and urine, the statistics show that 32.9% of the patients mistakenly use blood. _, including forgetting the correction before making the system, resulting in inaccurate measurement' affecting the money control. The aforementioned lack of inconvenience makes it difficult to make the time, thus visible spots, therefore, how to simplify or even eliminate the user's correction steps before measurement, but still maintain The accuracy of the measurement results is an improvement for the relevant industry. [New content] The term definition biosensor device refers to the combination of the electrochemical biosensor test paper provided by the creation to detect a special feature. A device for the concentration of substances such as a blood glucose meter, a fine alcohol meter, a uric acid meter, etc. The sensor end 6 refers to one end of the electrochemical biosensor test paper provided by the present invention in contact with the biosensor device. End-to-end means that the electrochemical biosensor test paper provided by the present invention is used at the end of the sample with the % of the sample, which is usually the end of the reaction zone, and is opposite to the sensor end. As mentioned in the figure, in order to save the user's calibration step before the measurement, but still can test the results of the 4 results, the paste provides an electrochemical biosensor test paper, whose towel contains - the number of H on the back of the substrate The component is used to automatically select the correcting parameter of the batch of test strips when the test strip is connected to the biosensor and device. _ Save the step of the step by the Wei line to simplify the overall measurement procedure. Inaccurate detection results due to omissions or operational errors. The technical means of the present invention is to provide an electrochemical biosensor test paper comprising a substrate, a front side and a back side, and a conductive layer. On a front surface of the substrate; a parameter identification component disposed at one end of the back surface of the substrate and configured to correspond to a specific set of correction parameter values; an upper spacer covering the conductive layer; and a reaction region, and The conductive layer is in contact and is used to carry out the reaction. In the preferred embodiment of the present invention, the parameter identification component in the electrochemical biosensor test paper provided by the present invention comprises four or more different blocks, and the parameter identification component can be connected or independent through each block. Forming a plurality of different patterns, and the maternal pattern corresponds to a specific set of correction parameter values, so when a test strip having a specific number of M380474 component elements is connected to a biosensor device, the device A set of correction parameter values corresponding to the batch of test strips can be automatically selected. The parameter identification component in the electrochemical bio-test strip provided by the better implementation of the solution includes a -block, a second block, a third block, and a fourth block. By the interconnection or independence of the four-sided blocks, the parameter identification elements in this creation can form 14 different aspects, and each pattern corresponds to a specific set of correction parameter values. The component of the electric scale provided by the present invention can be composed of a conductor; in the preferred embodiment, the parameter identification component is composed of carbon, and the parameter identification component is connected to each other. _ Lei secret engraved or knife money engraved into the district A. In the difficult _+, the wire contact element (4) 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 at least - the electrodes have - variable length regions. The variable length zone is used to adjust the length of the electrode, and the electric quantity of the electrode can be adjusted. t=j ^ The physical test paper is connected to the biosensor device. The scale, through the measurement of the resistance value, can be touched by her. The preferred embodiment is that the variable growth has a _ inferiority, so that the _independent biosensor device can be identified. In addition, in the case of better implementation, the electrode having the length of the financial variable is used as a reference electrode. In the electrochemical biosensor test paper provided by the present invention, the conductive layer comprises an 8 M380474 conductive silver layer and an i-carbon layer, and the conductive carbon layer covers the conductive layer. Each of the electrical layer electrodes is composed of a conductive carbon powder layer electrode and a conductive silver rubber layer. For example, the first electrode of the conductive layer is driven by the first electrode of the conductive silver kick layer and the conductive carbon to ride the first-missing domain, and the second impurity is shouted by the second electrode of the conductive silver-glue layer and the conductive carbonaceous second. This type of push. In the electrochemical biosensor test paper provided by the present invention, the electrode of the conductive layer is retracted by 'the end of the conductive layer at the end of the sensor and the end of the substrate at the end of the sensor. 1 to 1 mm. '(4) Electrochemical-free slit _ test paper is activated before the positive button is inserted into the biosensor device. In a preferred embodiment, the conductive layer comprises five electrodes, which are 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 region ′ for identifying the biosensor device in cooperation with the electrochemical biosensor test paper. And any two of the five electrodes of the conductive layer are connected to form a short circuit structure that initiates a biosensor device that is compliant to detect test paper results. For better implementation, the second electrode of the conductive layer is connected to the second electrode to form a short-circuit structure, and collectively serves as a reference electrode. In another preferred embodiment, the first electrode of the conductive layer is coupled to the second electrode of the conductive layer to form a short-circuit structure and collectively serves 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 reference electrode, and at least one of which is a working electrode. Preferably, the two electrodes are connected to form a common reference layer 7 and the other two electrodes are included, wherein the poles are respectively used to detect the blood glucose level of the sample t and the blood volume ratio electrode, and the rib_count is completely against The conductive layer comprises five electrodes, and the second electrode: the electrodes are connected to form an H reference electrode, and the second electrode of the fourth conductive layer is used to detect the first electrode of the conductive layer and the fifth electrode of the scale. For the working electrode. ―In another better implementation, the material ride includes five electrodes, wherein the conductive electrode is connected to the second electrode of the conductive layer to form a common reference electrode, and the second electrode of the electrical layer is an _electrode and the conductive layer is The four electrodes and the fifth electrode are working electrodes. In the creation of the Wei student's material, the four corners of the substrate are obtuse, and the _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ In the electrochemical biotechnology provided by the present invention, the step further comprises a partition covering the conductive layer and the β-knife substrate, and the middle partition is provided with a groove at the reaction end, and is longitudinally opened and π-direction The reaction end. The middle partition is further provided with an opening which is adjacent to the groove and does not communicate with the groove and threatens the reaction zone. In the electrochemical recording of the towel provided by the creation, the social partition corresponds to the opening of the middle partition - the opening for ventilation. The female upper partition is provided with a lack of 于 at the reaction end, _ good implementation of the financial, the fine _ _ 面 face shape. In addition, in the electrodiagnostic organism-test paper provided by the paste mine, the conductive carbon powder layer is provided at the reaction end paste. The gambling is to reduce the straight line, which is used to increase the coarseness of the substrate, prevent the material in the reaction zone from being removed, and increase the accuracy of the detection. In the electrochemical biosensor test paper provided by the present invention, the intermediate partition and the upper layer are further joined to the upper partition and the = board, and the transition layer is reduced by the towel partition. The groove and the portion are provided with a second groove. In the electrochemical biotest paper provided by the present invention, the method further includes: an insulating layer between the conductive layer and the cloth separator, wherein the insulating layer corresponds to the groove of the middle partition and A third recess is provided in the opening. ~ In summary, the electrochemical biosensor test paper provided by the present invention has the following beneficial effects as compared with the prior art and the existing products: - Electrochemical biosensor test paper and biosensing provided by the present creation When the device is connected, the device can automatically replenish the residual correction test paper-group correction parameter value, thereby eliminating the parameter correction step performed by the user, simplifying the overall measurement procedure, and avoiding the user's omission or operation error. The test result of the quasi bee. 1. Eliminate the additional manufacturing costs required to use a wafer card for calibration. ― Set 70 parameters to the back of the substrate to avoid co-location with the conductive layer on the front side of the substrate, and reduce the complexity and manufacturing cost of the test paper and the matching biosensor device in the design of the mechanism. Fourth, through the variable length of the electrode to identify the biosensor device combined with the paper, 'increased ease of use. Please refer to the attached drawings and details of the present disclosure and the following detailed description. In fact, on M380474, this work may be implemented in different forms' and should not be inferred to be limited to the examples mentioned in the text. [Embodiment] The first, second, and third figures are respectively a three-dimensional decomposition®, a three-dimensional upper shed, and a three-dimensional lower shed of the first embodiment. As shown in the first to third figures, the electrochemical bio-test paper provided by the present invention comprises a substrate (10) having a front surface (10) 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 (3〇) is disposed at the end of the back surface (1〇4) of the substrate (1〇4) and is corrected by a parameter specified by the singular-group; the upper spacer (10) is covered Above the conductive layer (20); and a reaction zone (8〇), in contact with the conductive layer (2〇) and used for the reaction. In addition, the electrochemical biosensor test paper provided by the present invention can be further divided into a sensor end (91) and a reaction end (92). The electrochemical biosensor test paper provided by the present invention allows the substrate (1 inch) to be a rectangular sheet, preferably having electrical insulation properties. In the preferred embodiment, the four corners of the substrate (10) are obtuse (12) to prevent the user from being stabbed or cut by the tip during operation. The conductive layer (20) is coated on the front surface (1〇2) of the substrate (10), and the conductive layer comprises a conductive silver paste layer (22) and a conductive carbon powder layer (24), the conductive carbon powder layer ( 24) Overlying the conductive silver paste layer (22). The conductive layer (2 〇) has two electrodes, and the three electrodes include at least one working electrode and one reference 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 used for mounting with the biosensor 12 M380474. Contact changes to detect changes in the electrochemical. In the preferred embodiment, the electrode of the conductive layer (20) is retracted such that the conductive layer (2〇) is at the end of the sensor end (91) and the substrate (1 〇) is at the sensor end (91). The ends are at a distance of 1 to 1 mm to prevent the electrochemical biosensor test paper from starting the device after it is properly inserted into the biosensor device. In a further embodiment, the conductive layer (2〇) is at a distance from the end of the sensor (91) to the end of the substrate (91) at the end of the sensor end (91) by 0.3 to 〇 8 mm; In the preferred embodiment, the conductive layer (2〇) is at the end of the sensor end (91) and the substrate (10) is at the end of the sensor end (91). 5 to 〇. 6 PCT. 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 partition (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 notch (44) is semi-circular or semi-deposited, and by the design of the notch (44), the area of the sample drawn into the reaction zone (10) is increased. Since the notch (44) increases the area in which the sample is inhaled, the sample can be sucked into the reaction zone (80) from the side parallel test strips, and can also be sucked into the reaction zone (10) from different angles above, thereby increasing the convenience of use. It also increases the speed at which the sample is inhaled, which in turn increases the accuracy of the test strip. The electrochemical bio-energy provided by this creation, Yu Gu (10), covers the substrate U0) and a part of the conductive layer (2〇), which contains bioactive substances (such as enzymes), enzyme cofactors, and stabilizers ( For example, a polymer) and a buffer solution are used to react with a sample. The fourth figure shows the shape of each electrode of the conductive layer in the first embodiment of the present invention. In this embodiment, the conductive layer (20) of the electrochemical biosensor test paper provided by the present invention comprises five electrodes, which are a conductive layer first electrode (2〇2) and a conductive layer second electrode ( 204) a conductive layer third electrode (206), a conductive layer fourth electrode (208) and a conductive layer fifth electrode (2〇9), and each conductive layer electrode is composed of a corresponding conductive carbon powder layer electrode And a conductive silver glue layer electrode, respectively, a conductive carbon powder layer first electrode (242), a conductive carbon powder layer second electrode (244), a conductive carbon powder layer second electrode (246), a conductive carbon a fourth electrode (248) of the powder layer and a fifth electrode (249) of a conductive carbon powder layer; a first electrode (222) of a conductive silver paste layer, a second electrode (224) of a conductive silver paste layer, and a conductive silver paste The third electrode (226), the fourth electrode (228) of a conductive silver paste layer and the fifth electrode (229) of a conductive silver paste layer, and one end of the five electrodes are longitudinal and parallel to each other. In addition, the second electrode (224) of the conductive silver paste layer has a variable length region (2240). In a preferred embodiment of the present invention, any two of the five electrodes of the conductive layer (20) are connected to form a short circuit structure. Referring to the fourth figure, in a further embodiment, the second electrode (2〇4) of the conductive layer is connected to the third electrode (2〇6) of the conductive layer to form a short-circuit structure and together serve as a reference electrode. In a preferred embodiment of the present 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 (208) of the conductive layer is a detecting electrode for determining whether the reaction zone has completely entered the reaction zone. In a preferred embodiment of the present invention, any of the five electrodes of the conductive layer (20) is a working electrode for detecting the blood glucose level of the sample. In a preferred embodiment M380474, the fifth electrode (209) of the V electrical layer is a working electrode β for detecting the blood glucose level of the sample. In the preferred embodiment of the present invention, five of the conductive layers (20) Either of the electrodes is a working electrode for detecting the blood volume ratio of the sample. In a preferred embodiment, the first electrode (202) of the conductive layer is a working electrode for detecting the blood volume ratio of the sample. 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 (104) of the substrate (10). Referring to the first and third figures, in a preferred embodiment, the parameter identification component (10) is disposed on the back side (104) of the sensor end (91) of the substrate (10) and on the front side of the substrate (10) ( The conductive layer (10) of 1〇2) is formed by the upper and lower relative position ribs being in contact with the biosensor/device. The fifth figure Α to Ν shows the various aspects of the parameter identification component (3〇) in this creation. In the electrochemical biosensor test paper provided by the present creation, the parameter identification component (10)) • contains more than four different blocks. In a preferred embodiment, the parameter identification component (30) includes four different blocks, namely a first block (31), a second block (32), and a third block (33). And a fourth block (34). Through the interconnection or independence of each block, the parameter identification component (10) in this creation can form 14 different states, and each state corresponds to a specific set of correction parameter values. In the present creation, the communication between the blocks of the parameter identification component (30) and the independent system are defined by laser etching or tool side division. The double dashed lines in the fifth diagrams A to N represent the interconnection between the blocks, and the double solid lines represent the mutual engraving and independence of each block. 15 Figure 5A shows the parameter identification component (30A) corresponding to the first set of correction parameter values, wherein the first block (31) and the second block of the parameter identification component (3〇A) (32) The third block (33) and the fourth block (34) are all connected to each other. Figure 5B shows a parameter identification component (30B) corresponding to the second set of correction parameter values, wherein the parameter identification component (3〇B) is the first block (31) and the second block ( 32) are interconnected and the third block (33) and the fourth block (34) are in communication with each other. Figure 5C shows a parameter identification component (30C) corresponding to the third set of correction parameter values, wherein the first block (3) of the parameter identification component (10) G) and the third block (33) are connected to each other. And the second block (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 second 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 independent of other blocks. And the second block (10), the third block (3), and the fourth block (10) are connected to each other. The fifth figure F is not the parameter identification component (30F) corresponding to the sixth set of correction parameter values, wherein the third block (10) of the parameter identification component (10)F is independently connected to other blocks and is - The block (8), the second block (10), and the fourth block (10) are connected to each other. The fifth graph G shows the parameter identification component corresponding to the seventh set of correction parameter values (the secret block 'where the fourth block (34) of the parameter identification component (30G) is independent of other blocks and the first A block (31), a second block (32) and a third block (33) are connected to each other. The fifth figure Η shows the parameter identification component (30Η) corresponding to the eighth set of correction parameter values. The second block (32) of the parameter identification component (30Η) is independently connected to other blocks and the first block (31), the third block (33) and the fourth block (34) are mutually The fifth block I shows the parameter identification component (301) corresponding to the ninth set of correction parameter values, wherein the first block (31) and the second zone of the parameter identification component (3〇1) The blocks (32) are connected to each other and the third block (33) and the fourth block (34) are each independently connected to each other. The fifth figure J shows the parameter identification elements corresponding to the tenth set of correction parameter values ( 30J) The aspect in which the third block (33) of the parameter identification component (3〇J) and the fourth block (34) are in communication with each other, and the first block (31) and the second block (32) are both Independent of each other The fifth figure K shows the parameter identification component (30K) corresponding to the eleventh set of correction parameter values, wherein the first block (31) and the third block of the parameter identification component (30K) 33) communicating with each other and the second block (32) and the fourth block (34) are each independently connected to each other. The fifth figure L shows the parameter identification component corresponding to the twelfth set of correction parameter values (30L) The second block (32) and the fourth block (34) of the parameter identification component (3〇L) are in communication with each other, and the first block (31) and the third block (33) are each Independently not connected to each other. 17 M380474 Figure 5 shows the parameter identification component (30Μ) corresponding to the thirteenth set of correction parameter values, where the parameter identifies the second block of the component (3〇Μ) ( 32) communicating with the third block (33) and the first block (31) and the fourth block (34) are each independently connected to each other. The fifth figure Ν shows the corrected parameter values with the fourteenth group. Corresponding parameter identification component (30Ν), wherein the first block (31) and the fourth block (34) of the parameter identification component (3〇Ν) are in communication with each other and the second block (32) and the Three blocks (33 Each of the electrodes is independently connected to each other. In the electrochemical biosensor test paper provided by the present invention, the parameter identification component (30) is composed of a conductor. In a preferred embodiment, the parameter identification component (3〇) is Composed of carbon. When a parameter identification component (3〇) having a specific aspect in the test paper is connected to the biosensor device, the device can recognize each block in the parameter identification component (3〇). In the connected or independent case, a set of correction parameter values corresponding to the parameter identification component (3〇) is automatically found. The first and second figures show the first electrode distribution, and the sixth figure β to ε is the various aspects of the second electrode variable length region (2240) of the conductive silver paste layer. The silver paste layer (22) is indicated by a broken line, and the conductive carbon powder layer (24) is indicated by a solid line. In a preferred embodiment of the present invention, the conductive layer second electrode (204) is connected to the conductive layer third electrode (2〇6) and can be used together as a reference electrode, and wherein the conductive silver adhesive layer is The two electrodes (224) have a variable length region (224 〇), and the difference in resistance values is used to identify the biosensor device that cooperates with the electrochemical (four) sensory paper. In a more preferred embodiment, the conductive silver paste layer second electrode variable length region M380474 (2240) has four different lengths. In Figure 6B, the second electrode variable length region (2 calendar) of the conductive silver paste layer has a full length, and the sensor end (10) of the second electrode (224) of the test layer is not connected. In the sixth figure c, the second electrode of the conductive silver paste layer can have a length of two-thirds of the length of the second region (22 shed), and the sensor end of the second electrode (224) of the conductive silver paste ( 91) 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 length, and is opposite to the sensor end of the second electrode (224) of the conductive silver paste layer. (9)) Unconnected_Connected. In Figure 6E, the variable length region of the second electrode of the conductive silver paste layer is completely missing' and is not connected to the sensor end (10) 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 (224G) of the conductive silver paste layer is inversely proportional to the resistance value of the electrode. The relationship 'that is, the longer the variable length region (measured) of the second electrode of the conductive silver paste layer, the lower the resistance of the hybrid. When the electrochemical bio-domain paper is connected to the biological > sensing device, the difference in resistance value caused by the difference in length of the second electrode variable length 11 (2240) of the conductive silver county can be discriminated. Electrochemical Bio-Test Paper is the test paper that is combined with the _ device. 7F of FIG. 7 is a second electrode distribution case in which the first electrode (2G2A) of the conductive layer (20A) is connected to the second electrode (leg) of the conductive layer to form a short-circuit structure, and is commonly used as a reference. The third electrode (leg) of the conductive layer is a thin electrode, and the fourth electrode (2〇8A) of the conductive layer is a working electrode for detecting the blood sugar level of the sample, the fifth electrode of the conductive layer ( 2 hidden) is a working electrode used to detect the sample 19 1V1J0U4/4 blood volume ratio. Referring to the second, B, C, D and E are the second electrode distribution cases of the second electrode in the case of the creation of the second electrode of the conductive shirt (2_ each), wherein the second electrode of the conductive silver layer (224A) having a variable length region (224Q). In the preferred embodiment, the conductive layer is a second electrode variable length region (2_ has four different lengths, and the conductive silver paste is shown in Figure B. The layered two-electrode variable length region (2) is substantially connected to the sensor end (91) of the second electrode (224a) of the conductive silver paste layer. The conductive silver county is shown in the seventh figure c. The second electrode variable length region (2240F) has a length of two-half of the total length and is not connected to the n-terminal (91) of the second electrode (224A) of the conductive silver paste layer. The seventh panel D shows the conductive The second electrode variable length region (2240G) of the silver paste layer has a length of one third of the total length and is not connected to the sensor end (91) of the second electrode (224A) of the conductive silver paste layer. In the £, the second electrode variable length region (224〇h) of the conductive silver paste layer is completely missing, and is not in phase with the sensor end (91) of the second electrode (224A) of the conductive silver paste layer. The eighth figure is an exploded perspective 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 include a cover layer and a portion of the substrate (20) 1 〇) upper middle partition (5 〇), wherein the middle partition (5 〇) is provided at the reaction end (92) with a groove (52) 'in the longitudinal direction and opening toward the reaction end (92). The middle partition (50) is provided with an opening (54). The opening (54) is adjacent to the groove (52) and does not communicate with the groove (52) and corresponds to the reaction zone (8〇). 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 thick seam section (240) 20 M380474 may be a straight line or a plurality of straight lines. The rough section (240) may be a conductive material, and the thick section (240) is more preferably formed of carbon powder. In addition, the rough section (240) may also be non- Made of conductive material. The rough section (240) is used to increase the roughness of the substrate (1〇), increase the adhesion strength of the reaction zone (80), and prevent the reaction zone (8〇). In a preferred embodiment of the present invention, the rough section (24〇) is located outside the near reaction zone (80). - The electrochemical biosensor test paper provided by the present invention may further comprise a An adhesive layer (60) between the partition (5〇) and the upper partition (40) for connecting the upper partition (40) and the middle partition (50). wherein the adhesive layer (6〇) Corresponding to the recess (52) and the opening (54) of the middle partition (5〇), a second recess (62) is provided. In the preferred embodiment of the present invention, the adhesive layer (60) It is composed of polyethylene terephthalate (PET) and coated with an adhesive material such as water glue on the upper and lower sides for bonding the upper partition (40) and the middle partition (5). 〇). The ninth drawing is an exploded perspective 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 (7〇) interposed between the conductive layer (20) and the middle partition (50), and The insulating layer (7〇) is provided with a third groove (72) corresponding to the groove (52) and the opening (54) of the middle partition (50). While the foregoing examples illustrate the specific facts of the present invention, any possible modifications and variations of the present invention are not inconsistent with the spirit and scope of the claims claimed. BRIEF DESCRIPTION OF THE DRAWINGS The first drawing is an exploded perspective view of a preferred embodiment of the present invention. The second drawing is a perspective top view of one preferred embodiment of the present invention. The second drawing is a perspective lower view of a preferred embodiment of the present invention. The fourth figure is the distribution of the electrodes of the conductive layer in a preferred embodiment of the present invention. The fifth figure A to N are various aspects of the parameter identification component in the present creation. The sixth figure A to E is the first electrode distribution case of the present invention and various aspects of the second electrode variable length region of the conductive silver paste layer. The seventh figure A to E are various aspects of the second electrode distribution trace and the second electrode variable length region of the conductive silver paste layer. The eighth figure is an exploded view of the preferred embodiment of the present invention. The ninth drawing is a perspective exploded view of yet another preferred embodiment of the present invention. [Description of main component symbols] 10: Substrate 102: Substrate front surface 104: Substrate back surface 12: Obtuse angle 20, 20A: Conductive layer 202, 202A: Conductive layer First electrode 204, 204A: Conductive layer Second electrode 22 M380474 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 second Electrode 2240, 2240A, 2240B, 2240C, 2240D, 2240E, 2240F, 2240G, φ 2240H: conductive silver paste layer second electrode variable length region 226: conductive silver paste layer third electrode 228: conductive silver paste 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 30C corresponding to the second group of correction parameter values : Corresponds to the third set of correction parameter values Parameter identification component 23 M380474 30D: Parameter identification component 30E corresponding to the fourth set of correction parameter values: Parameter identification component 30F corresponding to the fifth group of correction parameter values: Parameter identification component corresponding to the sixth group of correction parameter values 30G: parameter identification element 30H corresponding to the seventh group of correction parameter values: parameter identification element 301 corresponding to the eighth group of correction parameter values: parameter identification element 30J corresponding to the ninth group of correction parameter values: and tenth The parameter identification element 30K corresponding to the group correction parameter value: the parameter identification element 30L corresponding to the eleventh group of correction parameter values: the parameter identification element 30M corresponding to the twelfth group of correction parameter values: correction with the thirteenth group The parameter identification element 30N corresponding to the parameter value: the parameter identification element 31 corresponding to the fourteenth group of correction parameter values: first block 32: second block 33: third block 34: fourth block 40: Upper partition 42: opening 50: middle partition 54: opening 62: second recess 72: third recess 91: sensor end 44: notch 52: recess 60: adhesive layer 70: insulating layer 80 : Reaction zone 92: reaction end 24