五、新型說明： 【新型所屬之技術領域】 體斑’是指—種能夠讓檢 问數值精確度的生化感·。 捉 —以彺患者必須到醫院抽血檢查以作定期身體檢查，作 母次的檢查需要耗費許多時間，且來回奔波是相當累人及 耗神的’對於患者的身體又可能會造成其他負擔。 L先刚技術】 、-般來說’為了方便患者能隨時掌握自己的健康狀 況’市面上已有攜帶式或錢式的血液檢測裝置，患者。 要在檢測試片滴人檢體並與檢測試片上的反應膜^生^ 應’進而會產生不同的電喊，之後將檢測試片插進血液 檢測裝置内’檢測m卩會顯示檢測項目的數值，如此一 來，患者便可_制自身的身體狀況，且不需要為了抽 血檢查特地去醫院或驗_，具有相#程度的便利性。 —但如圖1及圖2所繪示的習知檢測試片la，包含一上 蓋體lla、-間隔層12a及-基體13a，上蓋體Ua及間隔 層12a依序貼設於基體13a上，基體13a印刷有二電極膜 131a及-導通電極膜132a，二電極膜1313各—端設有反應 膜134a，導通電極膜132a的一端連接二電極膜131a其中 之-。此種結構設計，由於二電極膜131a分別設有反應膜V. New description: [New technical field] The body spot refers to a kind of biochemical feeling that can make the numerical accuracy of the test. Catching - After the patient has to go to the hospital for a blood test for regular physical examination, it takes a lot of time for the mother to check, and it is quite tiring and consuming to go back and forth. 'The patient's body may cause other burdens. L first technology], in general, in order to facilitate patients to keep abreast of their own health conditions, there are portable or money-based blood test devices on the market, patients. It is necessary to test the test piece by dropping the human sample and reacting with the reaction film on the test piece to generate a different electric shout, and then insert the test piece into the blood detecting device. The value, in this way, the patient can make his own physical condition, and does not need to go to the hospital or test for the blood test, with the degree of convenience. The conventional test strip 1a as shown in FIG. 1 and FIG. 2 includes an upper cover body 11a, a spacer layer 12a and a base body 13a. The upper cover body Ua and the spacer layer 12a are sequentially attached to the base body 13a. The substrate 13a is printed with a two-electrode film 131a and a conductive film 132a. The second electrode film 1313 is provided with a reaction film 134a at each end, and one end of the conductive electrode film 132a is connected to the second electrode film 131a. This structural design is because the two electrode films 131a are respectively provided with a reaction film
ma的端部之間的距離過長，所以—般常見的情形為患者 滴入檢測試片la的的錢不足8夸，錢未能流佈二電極膜 131a上的反應臈134a，換言之，血液可能流經二電極膜】3U 4/18 M429096 的一端部之間的路途中，血液檢測裝置便產生相應之讀 • 值’此讀值並非是精確的檢測值，如此一來，容易造成判 • 讀上的錯誤。此外，既有的反應膜134a常用的為碳膜，一 般來說，單純使用碳膜做為反應媒介，使用時無法得到較 穩定的電流值。舉例來說，當使用者的血液濃度大小相異 時’所得到電流值的變動率相對幅度較大，也就是說，濃 度較大的血液，得到的電流值較大，相對地濃度較小時， 電流值則較小。藉此，電流不穩定同樣可能會產生讀值判 鲁 斷錯誤的問題。 ^緣是，本創作人有感上述問題之可改善，乃特潛心研 九亚配合學理之運用，終於提出一種設計合理且有效改善 上述缺失之本創作。 【新型内容】 你本創作之目的在於，提供一種生化感測器，透過參考 电極膜對反應膜上的檢體進行速度及血量分析並做適度校 正’可提高判斷檢體病理分析的精確度。The distance between the ends of the ma is too long, so it is common for the patient to drop the test strip la less than 8 quarts, and the money fails to flow through the reaction 臈134a on the second electrode film 131a, in other words, the blood may Flowing through the two-electrode film] During the path between the ends of 3U 4/18 M429096, the blood detection device produces a corresponding reading value. This reading value is not an accurate detection value, which makes it easy to cause a judgment. The error on the. Further, the conventional reaction film 134a is usually a carbon film. In general, a carbon film is simply used as a reaction medium, and a relatively stable current value cannot be obtained when used. For example, when the blood concentration of the user is different, the rate of change of the current value obtained is relatively large, that is, the blood having a larger concentration has a larger current value, and the relative concentration is smaller. , the current value is smaller. As a result, unstable currents may also cause problems with readout errors. The reason is that the creator feels that the above problems can be improved. He is dedicated to the use of the school in conjunction with the theory of science and technology, and finally proposes a design that is reasonable in design and effective in improving the above-mentioned defects. [New content] The purpose of your creation is to provide a biochemical sensor that analyzes the velocity and blood volume of the specimen on the reaction membrane through a reference electrode membrane and makes a moderate correction. This can improve the accuracy of the pathological analysis of the specimen. degree.
為了達成上述之目的，本創作提供一種生化感測器， 匕括一基體，其具有一07足丨1; I： ^印刷面，印刷面設有一反應膜、二 電極膜、一導通電極艇菸 Α ^ —不 版及一參考電極膜，導通電極膜位於 〜電極膜之間，導通雷极描土 胺並由 ，東極膜Λ近反應膜的一端連接二電極 ^ ^ >考电極膜與二電極膜其一相對設置於印刷 向的兩旁’反應膜且右 應胺;《势-八ρ ”有至^ 一第一金屬反應膜、非金屬反 〜金屬反應膜，二電極考電_的一端延伸地接觸第 第二金屬反_ = 1分別翻較屬反應膜及 h件’其設有至少一對應反應膜的 5/18 ==:蓋板，其設有至少-對應開口的檢測口，蓋 間且彼嫩咖與蓋板之 刷有於基體上印 速度及血h析並做適度校正，可提高判斷檢體病理 的精確度。料，分制二電極驗參考電_設有反庫 膜的端部之間的距離縮短，減少檢體流經路徑長度，藉: ’以提高其正確性。反應膜為金屬與非金屬 反應膜的組5，可提供較穩定的電流輸出值，具有減少檢 測時間的功效。 為能更進-步瞭解本創作的特徵及技術内容，請參閱 以下有關本創麵詳細說明與_，然而所關式僅提供 參考與說明用，並_來對本創作加以限制。 【實施方式】 以下所描;4之實闕有提及數量或其類似者，除非另 作說明，否則本創作的應用範疇應不受其數量或其類似者· 之限制。 [第一實施例] 請-併參考圖3、圖4及圖5所示，圖3及圖4分別所 繪示的為本創作生化感測器之第一實施例之立體分解及組 合圖，圖5為本創作生化感測器之第一實施例之使用狀態 之立體圖。本創作實施例揭露一種生化感測器i，其可插入 一多合一式的檢測襞置100,檢測裴置100具有一檢測入口 1001，片狀的生化感測器1可插入檢測入口 1〇〇1内，檢測 6/18 者的檢體^峨’㈣判斷使用 以衡量使用者身=三酸·旨等）， 中隔件12及—j; L匕感測器1包括一基體11、— 板13 π 而，生化感測器1是由上層的笔 隔件基體11及續於蓋板13與基體11之間的ΐ 及基體區:要利用虹吸原一 本創作的θ導通電_ 114及-參考電極膜115。 膜113、疋则印刷的方式將反紐112、二電極 的印刷面及參考電極膜115成型於基體11 其中所述電乾燥的反應酵素， 以是碳(C)、白金⑻弋：:，1二及茶考電極膜m可 不限定。其中斗几A、疋(g)電極，這裡對於材質並 極膜115及二it測器1插入檢測裝置100時，參考電 多個測試_==^定賴磁據，且能產生 請參考圖3取其千均值以增加準確度。 膜in之間，導5所不。導通電極膜1H位於二電極 提供檢測裝置1ΩΩ 1極膜114與檢測裝置⑽電性導通以 膜]12的的開機功能。導通電_削靠近反應 與二電極膜113 —電極膜113其中之-，參考電極膜115 膜m具有一第t相對設置於印刷面⑴的兩旁，反應 1122 屬反應臈1122及弟金屬反應膜1121、非金 置以各自保持1;金屬反應膜112 3彼此間相隔開設 、疋巨離。麥考電極膜115的一端延伸地 7/18 M429096 接觸第一金屬反應膜1121，二電極胺]n夂 电性犋113各一端分別接 非金屬反應膜1122及第二金屬反應膜1123，其中來考電 膜115可對反應膜112上的檢體進行速度及血量分析，二 對檢測裝置100產生相應數據做適度校正。 亚 這裡要補充說明的是，本創作的第一及第二金屬反鹿 膜112卜1123的材質較佳的為金屬「銀」，非金屬反應^ 1122的材質較佳的為非金屬「碳」，然而經由實驗得知，所 述第一及第二金屬反應膜1121、1123使用銀，而非金屬反 應膜1122使用碳的組配對於電流輸出的穩定性較好。換言 之，相較於先前的生化感測器，採樣使用者相同的血液濃 度進行檢測，本創作藉由上述第一、第二金屬反應膜1121、 1123及非金屬反應膜1122的使用材質及相對佈局設置，可 得到較高的電流輸出值，藉此.，就可避免血液濃度的不同， 以致電流值的變動率過大’易造成數據判斷失誤的問題產 生。然而，上述第一、第二金屬反應膜1121、1123及非金 屬反應膜1122所使用的材質為較佳的實施態樣，但實際上 藉由其他金屬及非金屬反應膜的搭配同樣可產生穩定電流 值的效益，藉此’對於第一、第二金屬反應膜H21、1123 及非金屬反應膜1122所使用材質並非只拘限於此，故凡屬 於相關領域熟悉該項技藝者所使用的材質變化皆應屬於本 創作的應用範疇内。 反應膜112主要是由第一金屬反應膜1121、非金屬反 應膜1122及第二金屬反應膜U23的組合，彼此間分隔交 錯的佈局方式可提供較穩定的電流輸出值，具有減少檢測 時間的功效’檢測時間較佳地可縮短至30秒以内，即可得 到量測數據。 8/18 M429096 中隔件12為-絕緣層’纽透明狀設置於基體u的 印刷面m上。中隔件η設有至少一對應反應膜112 口 m ’開口⑵具有-高度’使得反應膜112上的反 素限制於開π 121的圍親μ止反應酵素往外溢 出。補充說明-點’本創作的中隔件〗2所使用的材質可= 是聚W_yethylene，簡稱ΡΕ)、聚氯乙稀（㈣ CMoHde ’簡稱PVC )等高分子㈣，這㈣於㈣並不限 定。 4考圖3所不。本創作的蓋板]3具有親水性，蓋板 13設有至卜對應開口 121的檢測D 13卜肋供使用^ 的檢體經由檢測π 131滴入反應臈m上。蓋板Η及仲 咖11上，中隔件】2位於基體】】與; 板13之間且彼此之間互姆合㈣ 當基體Π進行印刷製程後，中二構換吕之， 緊接者蓋板13配合中 上’所述堆疊結構之_群可^^貼設於帽件】2 著=方式黏著，黏著方式在此並不用;·定面膠或者是液態黏 膜114及以二電極❹3、導通電極 然而，部分_人檢二1Q=2及蓋板13外， 二參具有，—參考電極延伸段川】及第 連接第一參考電第二參考電極延伸段1】52轉折地 1152接觸反應膜U2。又】】51，其中第二參考電極延伸段 二電極臈】13楣圭,丨盔 膜】】32，共同電極膜/、同電極膜1131及一量測電極 门電極㈣位於參考電極膜115與導通電極 M429096 ^ 之間旦其中共同電極膜1131的一端接觸非金屬反應 、，置測電極膜U32的一端接觸第二金屬反應膜 2」第共:電極膜】…具有_第一共同電極延伸段";; Π3；2#；；^Π& 11312，第二共同電極延伸段 θ蚵也連接第一共同電極延伸段11311。 一签里f電極膜1132具有""第—量測電極延伸段11321及 ===極延伸段11322，第二量測電極延伸段⑽2 轉:也連接量測電極延伸段11321， 2段1151 '第-共同電極延伸段则、導通電極= 與第=量測電極延伸段咖相互平行設置 膜 /二山同電極延伸段11312遠離第—共同電極延伸段 ，的-端鄰近第二量測電極延伸段11322，如此一來， 微小化反應膜112的設置面積，相較於先前技藝的反鹿膜 使Μ檢體流動路徑較長，容易導致^ 固反應膜時檢測裝置便產生相應數值，此時的 ==差較大的量測數據’較缺乏參考價值。然 1，之___’使用時將檢體由檢測口⑶滴入反 體利用虹吸原理可—次到位遍及整個反應 朕m，此=篁測數據誤差範圍較小，精確度可大幅提升。 第一參考電極延伸段1151、第 1131卜導通電極膜114及第一量 、』电栓U甲半又 間等距設置。 詩电極延伸段湖彼此 —蓋==至少一缺口132及一透明層133,缺口132 相^板13邊緣，透明層133位於缺〇132,檢測口 131 設置於透明層133’透明層133用以觀測使用者檢體於反應 10/18 蔣112上的遍佈情形。透明層133與基體 Γ開，透明層133、開〇 121及基體η的印刷面= =成-檢體流細未標號），檢測D 131與檢體流道堆= 向^檢體流道的流方向係與導通電_ ιΐ4的延“ 開口 121具有一第一寬度1211及一第二 一 一 ^121]大於第二寬度1212 ’檢體流道係、“ ’弟 [第二實施例] 夕 請參考圖6所示，圖6為本創作生化感測 立體分解圖。本實施例相較於上述實施例= f ^上Γ電極膜113及參考電極膜U5㈣局2 。谷例來說’二電極瞑113與參考電極膜m皆^ :料型，且彼此間分開地平行設置，其中共同電極二⑶ 二端=非金屬反麵1122，量測電極膜113二 =金屬反應膜1123。藉此，將基體U : 電：Γ的佈局簡易化，具有降低印刷所‘ 極_成本之優勢。_相較於第—實施例，本實 j極膜⑴及參考電極膜m設有反應膜m的端部之 離較長’換言之，檢體流祕縣度較長，如此-“’而要較多的檢體採樣才可流佈整個反應膜丨12。但由於 本實施例的反應膜112所使用的材質及其於印刷面⑴上 的佈局方式（意即非金屬反應膜1122 位於第一及第二八屬 反應膜⑽、]123之間），可讓電流值的輸出穩定= 樣具有提鬲讀值判斷精確度之功效。 立匕再。月荟考圖3及圖$所示，為了清楚地說明本創作之 意指’以下提供内容為本創作生化感測器丨的製作過程。 11/18 M429096 首先，基體11固定於一固定治具(圖略)上； 基體11同時印刷反應m 112、二電極膜ιΐ3、導通電 極膜114及參考電極膜115 ; 112 於基體^反應膜112上方的中隔件12以黏貼合的方式貼設 將液邊的反應酵素以噴人或擠壓的方式覆蓋反應膜 f 呈現乾燥反應酵素至少25分鐘或以上直到反應酵素 把蓋板13配合令隔杜 於中隔件12 ； 12的形狀以黏貼合的方式貼設 最後將基體Π做單仿共丄 使用時，檢體滴人反預定的長條狀結構。 素與檢體起電化學反應時，_、，§反應版112的反應酵 115會測得多個傳遞訊於，僂極膜113會與參考電極膜 並換算出待測物(如血_^=號會傳導到檢測裝置⑽ 據值的差異度並不大，則"測數據值，若該等檢测數 據值。若該等檢測數據值的差測物的血糖數 量可能有所不足。 W異度過大，射欺待測血 例如另特:說1的是’本創作提及的方向用語， 方向。因此，使用的方向等’僅是參考附加圖式的 本創作。 用5 °疋用來說明而並非用來限制 綜合上述，本創作關 刷有參考電極膜，这過參考器，於基趙上印 速度及血量分析並做適度二，膜，應膜上的檢題進行 ^ ^ ，可提高判斷檢體病理分柝 12/18 M429096 的精確度。此外，分別將二電極膜及參考電極膜設有反應 膜的端部之間的距離縮短，減少檢體流經路徑長度，藉以 縮小讀值誤差，以提高其正確性。反應膜為金屬與非金屬 反應膜的組合，可提供較穩定的電流輸出值，具有減少檢 測時間的功效。 .惟以上所述僅為本創作之較佳實施例，非意欲侷限本 創作的專利保護範圍。 【圖式簡單說明】 圖1為習知生化感測器之立體分解圖。 圖2為習知生化感測器之立體組合圖。 圖3為本創作生化感測器之第一實施例之立體分解圖。 圖4為本創作生化感測器之第一實施例之立體組合圖。 圖5為本創作生化感測器之第一實施例之使用狀態之立 體圖。 圖6為本創作生化感測器之第二實施例之立體分解圖。 【主要元件符號說明】 [本創作] 1生化感測器 11基體 111印刷面 112反應膜 1121第一金屬反應膜 1122非金屬反應膜 1123第二金屬反應膜 13/18 M429096 113電極膜 1131共同電極膜 11311第一共同電極延伸段 11312第二共同電極延伸段 1132量測電極膜 11321第一量測電極延伸段 11322第二量測電極延伸段 114導通電極膜 115參考電極膜 1151第一參考電極延伸段 1152第二參考電極延伸段 12中隔件 121 開口 1211第一寬度 1212第二寬度 13蓋板 131檢測口 132 缺口 133透明層 100檢測裝置 1001檢測入口 [習知技術] 1 a檢測試片 11a上蓋體 12a間隔層 13a基體 14/18 M429096 131a電極膜 132a導通電極膜 134a反應膜In order to achieve the above object, the present invention provides a biochemical sensor, comprising a substrate having a 07 enough ;1; I: ^ printing surface, the printing surface is provided with a reaction film, a two-electrode film, and a conductive electrode boat smoke Α ^ - no plate and a reference electrode film, the conduction electrode film is located between the ~ electrode film, conducts the thunder magnetic amine and is connected to the two electrodes at one end of the east film Λ near the reaction film ^ ^ > The two-electrode film is disposed opposite to the two sides of the printing film and the right amine; the potential-eight ρ has a first metal reaction film, a non-metal reverse metal reaction film, and the second electrode is _ One end of the second metal is in contact with the second metal opposite _=1, respectively, which is opposite to the reaction film and the h piece, which is provided with at least one corresponding reaction film of 5/18 ==: a cover plate, which is provided with at least a corresponding opening detection The mouth, the cover and the brush of the penny and the cover plate have the printing speed and blood analysis on the substrate and make a proper correction, which can improve the accuracy of judging the pathology of the sample. The distance between the ends of the anti-membrane film is shortened, and the length of the sample flow path is reduced, by: ' Improve the correctness. The reaction film is a group 5 of metal and non-metal reaction film, which can provide a stable current output value and reduce the detection time. In order to further understand the characteristics and technical content of this creation, please Please refer to the following for a detailed description of the wound and _, however, the reference only provides reference and explanation, and _ to limit the creation. [Embodiment] The following description; 4 the actual number mentioned or similar Unless otherwise stated, the scope of application of this creation shall not be limited by its number or the like. [First Embodiment] Please - and refer to Figures 3, 4 and 5, Figure 3 and Figure 4 is a perspective exploded view and a combined view of the first embodiment of the biochemical sensor, and FIG. 5 is a perspective view showing the state of use of the first embodiment of the biochemical sensor. The present embodiment discloses A biochemical sensor i can be inserted into an all-in-one detecting device 100. The detecting device 100 has a detecting inlet 1001, and a sheet-like biochemical sensor 1 can be inserted into the detecting inlet 1〇〇1 to detect 6 /18 The body of the test ^峨' (four) judgment Used to measure the user's body = triacid, etc., the spacers 12 and -j; the L匕 sensor 1 includes a substrate 11, a plate 13 π, and the biochemical sensor 1 is separated by the upper pen The substrate 11 and the ΐ and the substrate region between the cover plate 13 and the substrate 11 are: the θ conduction current _ 114 and the reference electrode film 115 are created by siphoning. The film 113 and 疋 are printed in the opposite manner. The printing surface of the button 112 and the reference electrode film 115 are formed on the substrate 11 wherein the electrically dried reaction enzyme is carbon (C), platinum (8) 弋::, 1 and the tea electrode film m is not limited. Among them, there are several A and 疋 (g) electrodes. Here, when the material and the polar film 115 and the two measuring device 1 are inserted into the detecting device 100, the reference electric test _==^ depends on the magnetic data, and can be generated. 3 Take its thousand mean value to increase the accuracy. Between the membranes, the guide 5 does not. The conducting electrode film 1H is located at the two electrodes to provide a starting function of the detecting device 1 Ω Ω 1 pole film 114 and the detecting device (10) electrically conducting the film 12 . Conduction_cutting close to the reaction and the two-electrode film 113 - among the electrode films 113, the reference electrode film 115 has a t-th oppositely disposed on the printing surface (1), and the reaction 1122 belongs to the reaction 臈 1122 and the young metal reaction film 1121 The non-gold is kept at 1 each; the metal reaction film 112 3 is spaced apart from each other, and is separated from each other. One end of the McCaw electrode film 115 is extended to 7/18 M429096 to contact the first metal reaction film 1121, and the two ends of the two electrode amines are electrically connected to the non-metal reaction film 1122 and the second metal reaction film 1123, respectively. The test film 115 can perform speed and blood volume analysis on the sample on the reaction film 112, and the second pair of detecting devices 100 generate corresponding data for moderate correction. It should be added here that the material of the first and second metal anti-deer film 112 1123 of the present invention is preferably metal "silver", and the material of non-metal reaction ^ 1122 is preferably non-metal "carbon". However, it has been experimentally found that the first and second metal reaction films 1121, 1123 use silver, and the non-metal reaction film 1122 uses carbon combination for better stability of current output. In other words, compared with the previous biochemical sensor, the sample user has the same blood concentration for detection, and the material and relative layout of the first and second metal reaction films 1121, 1123 and the non-metal reaction film 1122 are used in the present creation. The setting can obtain a higher current output value, thereby avoiding the difference in blood concentration, so that the rate of change of the current value is too large, which may cause a problem of data misjudgment. However, the materials used in the first and second metal reaction films 1121, 1123 and the non-metal reaction film 1122 are preferred embodiments, but in practice, the combination of other metal and non-metal reaction films can also be stabilized. The benefit of the current value is that the materials used for the first and second metal reaction films H21 and 1123 and the non-metal reaction film 1122 are not limited thereto, and therefore the materials used by those skilled in the relevant art are changed. All should fall within the scope of application of this creation. The reaction film 112 is mainly composed of a combination of the first metal reaction film 1121, the non-metal reaction film 1122 and the second metal reaction film U23, and the layout pattern is alternately staggered to provide a relatively stable current output value, and has the effect of reducing the detection time. 'The detection time can be shortened to within 30 seconds, and the measurement data can be obtained. 8/18 M429096 The spacer 12 is an insulating layer disposed on the printing surface m of the substrate u in a transparent manner. The spacer η is provided with at least one corresponding reaction film 112. The mouth opening (2) has a height - such that the counter-reaction on the reaction film 112 is restricted to the π-121 open-closed reaction enzyme. Supplementary explanation - The material used in the "Separator" of this creation can be = poly (W_yethylene, ΡΕ), polyvinyl chloride ((4) CMoHde 'referred to as PVC) and other polymers (4), which is not limited to (4) . 4 is not shown in Figure 3. The cover plate 3 of the present invention is hydrophilic, and the cover 13 is provided with a detection D corresponding to the opening 121. The sample for use of the rib is dropped onto the reaction 臈m via the detection π 131 . On the cover plate and the secondary coffee 11, the spacers 2 are located in the base] and the plates 13 and are mutually connected to each other. (4) After the substrate is printed, the second structure is changed to Lv, and the close The cover plate 13 is matched with the upper middle part of the stacking structure, and can be attached to the cap member. 2 The method is adhered to the method, and the adhesive method is not used here. · The fixed surface glue or the liquid mucous membrane 114 and the two electrodes ❹ 3 And the conduction electrode, however, the part _ human inspection 2 1 = 2 and the cover plate 13 , the second reference has - the reference electrode extension section and the first connection reference second reference electrode extension section 1] 52 turns of the ground 1152 contact Reaction film U2. [51], wherein the second reference electrode extension segment two electrodes 楣 13 楣 丨, 丨 丨 膜 】 】 32, common electrode film /, the same electrode film 1131 and a measuring electrode gate electrode (four) located in the reference electrode film 115 When one end of the common electrode film 1131 is in contact with the non-metal reaction, the one end of the electrode film U32 contacts the second metal reaction film 2". The common electrode film has a _ first common electrode extension. ";;Π3;2#;; ^ Π & 11312, the second common electrode extension θ 蚵 is also connected to the first common electrode extension 11311. The f-electrode film 1132 has a ""-measurement electrode extension 11321 and === pole extension 11322, and the second measurement electrode extension (10) 2 rotation: also connects the measurement electrode extension 11321, 2 segments 1151 'the first common electrode extension section, the conduction electrode = is parallel with the first measurement electrode extension section, and the membrane/two mountain same electrode extension section 11312 is away from the first-common electrode extension section, and the - end adjacent to the second measurement The electrode extending portion 11322, in this way, the setting area of the miniaturized reaction film 112 is longer than that of the prior art anti-deer film, so that the detection device generates a corresponding value when the reaction film is solid. At this time, the measurement data with larger == difference is less reference value. However, when ___' is used, the sample is dropped from the detection port (3) into the reverse body. The siphon principle can be used to pass the entire reaction 朕m. This = the data error range is small and the accuracy can be greatly improved. The first reference electrode extension 1151, the 1131th conductive film 114, and the first amount, the "electropile U" are disposed equidistantly. The poem electrode extension section lakes mutually cover-== at least one notch 132 and a transparent layer 133, the notch 132 is on the edge of the plate 13, the transparent layer 133 is located in the defect 132, and the detection port 131 is disposed on the transparent layer 133' transparent layer 133 To observe the spread of the user's specimen on the reaction 10/18 Chiang 112. The transparent layer 133 is separated from the substrate, and the printing surface of the transparent layer 133, the opening 121 and the substrate η == into the sample stream is not labeled, and the detection of D 131 and the sample flow path stack = the flow path of the sample body The flow direction system and the conduction current _ ιΐ4 extension "the opening 121 has a first width 1211 and a second one-one ^ 121] is greater than the second width 1212 'sample flow path system, "'di [second embodiment] eve Please refer to FIG. 6 , which is a three-dimensional exploded view of the biochemical sensing. This embodiment is compared with the above embodiment = f ^ upper electrode film 113 and reference electrode film U5 (four). In the case of the valley, the 'two-electrode 瞑 113 and the reference electrode film m are both: material type, and are arranged in parallel with each other, wherein the common electrode two (3) two ends = non-metal reverse surface 1122, the measurement electrode film 113 = metal Reaction film 1123. Thereby, the layout of the substrate U:Electrical:Γ is simplified, and the advantage of reducing the cost of the printing unit is reduced. Compared with the first embodiment, the actual j-electrode film (1) and the reference electrode film m are provided with a longer end portion of the reaction film m. In other words, the sample flow is longer in the county, so - A large amount of sample sampling can flow through the entire reaction film 丨12. However, due to the material used in the reaction film 112 of the present embodiment and its layout on the printing surface (1) (that is, the non-metal reaction film 1122 is located first and The second and eighth genus reaction membranes (10) and ]123 can stabilize the output of the current value. The sample has the effect of judging the accuracy of the reading value. The 匕 匕 。 月 月 月 月 月 月 月 月 月 月 月 月 月 月 月 月 月Explain clearly that the meaning of this creation means 'the following content is the production process of the biochemical sensor 创作. 11/18 M429096 First, the substrate 11 is fixed on a fixed fixture (figure omitted); the substrate 11 simultaneously prints the reaction m 112, the two-electrode film ιΐ3, the conductive electrode film 114 and the reference electrode film 115; 112 the spacers 12 above the substrate reaction film 112 are adhered to the liquid-side reaction enzyme to spray or squeeze The method covers the reaction membrane f to present the dry reaction enzyme for at least 25 minutes or more until The reaction enzyme binds the cover plate 13 so that the shape of the partition member 12 is attached in an adhesive manner, and finally the base body is used as a single imitation conjugate, and the sample is dropped into a predetermined long strip structure. When the element reacts with the sample electrochemically, the reaction solution 115 of the reaction plate 112 of the _, § reaction plate 112 will measure a plurality of transmissions, and the gate film 113 will be converted with the reference electrode film and the object to be tested (such as blood _^ The number will be transmitted to the detection device (10). The difference in the value of the data is not large. Then, the data value is measured. If the value of the test data is different, the blood glucose level of the difference may be insufficient. W is too large, and the bully is to be tested for blood, for example, the special one is: 'The direction of the term mentioned in this creation, direction. Therefore, the direction of use, etc.' is only the reference to the additional schema of this creation. With 5 °疋Used for illustration and not for limiting the above, the creation brush has a reference electrode film, which passes through the reference device, and prints the velocity and blood volume on the base Zhao and does a moderate degree. The film should be examined on the film. ^ ^ It can improve the accuracy of judging the pathological score of the specimen 12/18 M429096. The distance between the end portions of the two electrode film and the reference electrode film provided with the reaction film is shortened, and the length of the sample flow path is reduced, thereby reducing the reading error to improve the correctness. The reaction film is a metal and a non-metal reaction film. The combination can provide a relatively stable current output value and has the effect of reducing the detection time. However, the above description is only a preferred embodiment of the present invention, and is not intended to limit the scope of patent protection of the creation. [Simplified illustration] 1 is a perspective exploded view of a conventional biochemical sensor. Fig. 2 is a perspective assembled view of a conventional biochemical sensor. Fig. 3 is an exploded perspective view of the first embodiment of the biochemical sensor. A three-dimensional combination of the first embodiment of the biochemical sensor is created. Fig. 5 is a perspective view showing the state of use of the first embodiment of the biochemical sensor. 6 is an exploded perspective view of a second embodiment of the biochemical sensor of the present invention. [Main component symbol description] [This creation] 1 Biochemical sensor 11 substrate 111 printing surface 112 reaction film 1121 first metal reaction film 1122 non-metal reaction film 1123 second metal reaction film 13/18 M429096 113 electrode film 1131 common electrode Membrane 11311 first common electrode extension 11312 second common electrode extension 1132 measurement electrode film 11321 first measurement electrode extension 11322 second measurement electrode extension 114 conduction electrode film 115 reference electrode film 1151 first reference electrode extension Segment 1152 Second Reference Electrode Extension 12 Separator 121 Opening 1211 First Width 1212 Second Width 13 Cover Plate 131 Detection Port 132 Notch 133 Transparent Layer 100 Detection Device 1001 Detection Entrance [Prior Art] 1 a Test Specimen 11a Upper cover 12a spacer 13a base 14/18 M429096 131a electrode film 132a conductive film 134a reaction film
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