1252919 玖、發明說明： 【赉明所屬之技術領域】 ，發明係關於一種核酸生物感測裝置及 法，尤才曰—種適用於石英晶體微 ^製備方 物感測裝置及其製備方法。 +物-之核酸生 【先前技術】 ίο 15 科技之輕薄短小化趨勢，加上資訊處理 «電近年來蓬勃的發展，其中最受喝目；生= :::充’其要求的不僅要準確，更要講求快速二= ^物中毒時病原菌之檢測，就需要即時： 錢;然而，傳統檢測系統如酵素固定檢測法4 = 3-5·工你不 书而粍費 南/刀子酶檢測系、統也需要12-24小時的時 -：：；Γ 生物感測器是最新發展出的一種檢測方式，其獨特之 構係來自生物體本身，其所具備之高特 门巫又回4擇性以及即時輸出等特性，而可利 材料本身作為感測器或探針構造的部分；可應 :九領域包括藥物開發、醫療檢驗與環境檢測等。早期的 ^展是利用細胞、组織甚至微生物，與變換器整合起來將 物反應轉換到數位電子訊號，主要所使用的變 學、網測溫度的方式；而下一代的生物感測器則是 Μ理加上璧電和磁性變能器，可即時傳遞 20 1252919 有關抗原_抗體、細胞受器（receptor)與配體（ligand)，或是 DNA與RNA核酸序列互補的鍵結等資訊，所採用的方法 如表面電漿共鳴技術（surface plasma resonance)、電化學及 壓電質量檢測等，正朝著縮短檢測時間、提高檢測靈敏度 專方面改σ如表面電漿共鳴技術目前已發展至可於1 · 5 小時檢測完畢，而偵測極限可達1(Γΐ、/Ηζ，可利用於量測 血糖值，偵測環境中污染源與殺蟲劑，檢測食品病原菌， 生物戰劑等。 石英日日體 4 天平（Quartz cryStal micr〇balance，QCM)為 1〇 :質置感測元件，於石英板兩邊通常為兩片金屬電極，如 金:銀、紹或鎳，其主要作用在沿晶片表面垂直方向導入 ^ m 迫使曰曰體内部結晶格子產生類似立波的機械 震盈，如Μ板的厚度一t，此種機械式震盪可以以一定 名頁之頻率表現出，再藉著導入一適當震盪電路而量測出諧 振頻率（res〇nant frequency)。電極質量及外加附著在電極 上之4膜貝$變化將是改變晶體頻率的最大因素，因此於 QCM辰盪凡件表面塗敷一層可辨識生物分子之材料，在吸 生物分子時，表面重量增加，則可測得之震盪頻率將1252919 玖, invention description: [Technology field of 赉明], the invention relates to a nucleic acid biosensing device and method, and the invention is applicable to a quartz crystal micro-preparation device sensing device and a preparation method thereof. + material - the nucleic acid [previous technology] ίο 15 The trend of technology is light and thin, coupled with information processing «Electricity has developed vigorously in recent years, the most popular among them; Health = ::: It is necessary to stress the detection of pathogens in the rapid two = ^ poisoning, you need immediate: money; however, the traditional detection system such as enzyme immobilization detection method 4 = 3-5 · work you do not book and Fei Nan / knife enzyme detection system The system also needs 12-24 hours -::; Γ Biosensor is the latest development of a detection method, its unique structure comes from the organism itself, and its high-tech witch is back to 4 Characteristics such as sex and instant output, and the material itself is part of the sensor or probe construction; it can be: nine areas including drug development, medical testing and environmental testing. The early stage of the exhibition is the use of cells, tissues and even microorganisms, combined with the converter to convert the material reaction to digital electronic signals, mainly using the way of changing the temperature and measuring the temperature of the net; the next generation of biosensors is Μ 璧 璧 和 和 和 和 和 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 12 Methods such as surface plasma resonance, electrochemistry and piezoelectric quality testing are improving the detection time and improving the detection sensitivity. For example, surface plasma resonance technology has been developed to 1 · 5 hours detection, and the detection limit can reach 1 (Γΐ, /Ηζ, can be used to measure blood sugar levels, detect pollution sources and pesticides in the environment, detect food pathogens, biological warfare agents, etc. Quartz day body 4 (Quartz cryStal micr〇balance, QCM) is 1〇: the mass sensing element, usually two metal electrodes on both sides of the quartz plate, such as gold: silver, Shao or nickel, which mainly acts along the edge. The vertical direction of the wafer surface is introduced to force the internal crystal lattice of the crucible to produce a mechanical shock similar to the vertical wave. For example, if the thickness of the raft is one t, the mechanical oscillation can be expressed at a certain frequency of the page, and then by introducing a Appropriate oscillating circuit to measure the resonant frequency (res〇nant frequency). The electrode mass and the addition of 4 membranes attached to the electrode will be the biggest factor to change the crystal frequency, so apply a layer on the surface of the QCM The material of the biomolecule can be identified. When the surface weight is increased when the biomolecule is absorbed, the oscillating frequency can be measured.
Ik著吸附物重量與其他性質而成比例變化，❿可為一適當 20 之生物感測器。 【發明内容】 本t明之主要目的係在提供一種核酸生物感測裝置 及其製備方法。 1252919 及直製借ϋ另&目的係在提供一種核酸生物感測裝置 及其裏備方法，俾能{士人兩攸 ^ ^ ^ ^…&電水沈積法，提供一新穎之核酸 导木針固疋法，以製借ψ — 、 #出一具備鈿短檢測時間、且提高檢測 莖敏之核i文生物感剛裝置 檢測系統。 俾月4供-即時且準確的生物 為達成上述目的，本發明核酸生物感測裝置之製備方 法’其步驟包括：(a)提供一含金屬電極之墨電基材；⑻ 、電水沈積法沈積—有機金屬矽薄膜於該壓電基材或該金 屬電極上；（C)固定—交聯劑於該有機石夕薄膜上；以及⑷ 10固定-生物物質於帶有該交聯劑之有機石夕薄膜表面上。 /本發明核酸生物感測裝置中適用之壓電基材不限，較 佳係石英晶體微天平質量感測元件或表面聲波元件；適用 之生物物質不限，較佳是核酸或蛋白質，更佳係核酸；本 發明所使用之電漿沈積法之電漿能量不限，較佳係介於 15 5-50瓦特之間，處理之時間不限，較佳係小於％分鐘；本 方法於步驟（b)之後更可選擇性地包括一步驟（bi)，進行光 表面接枝聚合，使其所使用之有機材料可於表面形成一均 勻的親水性薄膜；本發明方法於步驟（bl)中，所適用於進 行光表面接枝聚合之材料不限，較佳係帶胺基或酸基之有 20機材料，最佳係丙烯醯胺（Acrylamide，AAm)或異康酸 (ItaCOnicacid)，且可形成一親水性薄膜；進行光表面接枝 聚合所使用之光不限，較佳係UV光，且適用之能量不限， 車父佳係500-1000瓦特之間，且照射時間不限，較佳為 分鐘。 1252919 本發明方法於步驟(bl)之後，更可包括一步驟(b2)，、A 加擴增劑於該接枝聚合完成之表面，以增加該表面 之胺基量，增進後續步驟⑷進行之生物物質之交聯效果， =中剌之胺基擴增劑不限，較佳係—帶胺基之有機物 f取仏係PEI(p〇lyethyleneimine)。本發明適用之交聯劑 最佳係戊二醛，且所使用之濃度不限，較佳係低於2.5〇/〇: 本發明亦包括-種核酸生物感測裝置，其結構包括·· ίο 15 ^ s金屬電極之壓電基材；—有機石夕薄膜，係沈積於該壓 電基材或該金屬電極上；—交聯劑層，係固定於該有機金 夕薄膜上，以及一生物物質，係固定於該交聯劑層上。 ^本發明核酸生物感測裝置適用之壓電基材不限，較佳 係石英晶體微天平質量感測元件或表面聲波元件；本發明 核酸生物感測裝置適用之生物物質不限，可以是核酸片段 或蛋白貝，較佳係核酸片段；本發明之核酸生物感測裝置 於該有機矽薄膜上，可更包括一光表面接枝聚合層，以使 其所使用之有機材料可於有機矽薄膜表面形成一均勻的親 水性薄膜；適用之有機材料不限，較佳係一由帶胺基或酸 基之烯化合物聚合而成之親水性薄膜，該帶胺基或酸基之 烯化合物最佳為丙烯醯胺或異康酸；本發明於光表面接枝 聚合層上更可包括一胺基擴增劑層，以增加表面胺基量， 增進生物物質之交聯效果，胺基擴增劑所使用材料不限， 較佳係帶胺基之有機化合物，最佳係 PEI(p〇lyethyleneimine)。本發明之交聯劑最佳係戊二醛。 20 1252919 【實施方式】 為能讓貴審查委員能更瞭解本發明之技術内容，特 舉數較佳具體實施例說明如下。Ik is proportional to other properties, and can be a suitable biosensor. SUMMARY OF THE INVENTION The main object of the present invention is to provide a nucleic acid biosensing device and a method of preparing the same. 1252919 and the direct system of the other is to provide a nucleic acid biosensing device and a preparation method thereof, and the invention can provide a novel nucleic acid guide by using the method of electro-hydraulic deposition. The wooden needle solid-fixing method is used to make a ψ-, ## a detection system with a short detection time and an improved nuclear detection device for detecting stem sensitivity.俾月4供- Instant and accurate organisms for the above purposes, the preparation method of the nucleic acid biosensing device of the present invention's steps include: (a) providing a metal-electrode-containing ink-electric substrate; (8), electro-hydraulic deposition method Depositing an organometallic ruthenium film on the piezoelectric substrate or the metal electrode; (C) fixing-crosslinking agent on the organic zeolitic film; and (4) 10 fixing-biological substance in the organic layer having the crosslinking agent Shi Xi film on the surface. The piezoelectric substrate suitable for use in the nucleic acid biosensing device of the present invention is not limited, and is preferably a quartz crystal microbalance mass sensing element or a surface acoustic wave element; the applicable biological substance is not limited, preferably a nucleic acid or a protein, preferably The nucleic acid of the plasma deposition method used in the present invention is not limited, preferably between 15 5-50 watts, and the treatment time is not limited, preferably less than % minutes; the method is in the step ( b) optionally further comprising a step (bi) for performing photosurface graft polymerization such that the organic material used forms a uniform hydrophilic film on the surface; the method of the invention is in step (bl), The material suitable for the grafting polymerization of the optical surface is not limited, and preferably has a melamine or acid group of 20 materials, preferably Acrylamide (AAm) or Isaconic acid (ItaCOnicacid), and Forming a hydrophilic film; the light used for grafting polymerization on the surface is not limited, preferably UV light, and the applicable energy is not limited, the car is between 500-1000 watts, and the irradiation time is not limited. Good for the minute. 1252919 The method of the present invention may further comprise a step (b2) after the step (b1), adding an amplification agent to the surface of the graft polymerization to increase the amount of the amine group on the surface, and promoting the subsequent step (4). The cross-linking effect of the biological substance, = the amino-based amplifying agent of the cerium is not limited, and preferably the organic-based substance f is taken from the PEI (p〇lyethyleneimine). The cross-linking agent to which the present invention is applied is preferably glutaraldehyde, and the concentration used is not limited, preferably less than 2.5 〇/〇: The present invention also includes a nucleic acid biosensing device, the structure of which includes ·· ίο a piezoelectric substrate of 15 ^ s metal electrode; an organic stone film deposited on the piezoelectric substrate or the metal electrode; a crosslinking agent layer fixed on the organic gold film, and a living body The substance is immobilized on the crosslinking agent layer. The piezoelectric substrate to which the nucleic acid biosensing device of the present invention is applied is not limited, and is preferably a quartz crystal microbalance mass sensing element or a surface acoustic wave element; the biological material applicable to the nucleic acid biosensing device of the present invention is not limited, and may be a nucleic acid The fragment or protein shell is preferably a nucleic acid fragment; the nucleic acid biosensing device of the present invention may further comprise a light surface graft polymer layer on the organic germanium film, so that the organic material used can be used in the organic germanium film. Forming a uniform hydrophilic film on the surface; suitable organic materials are not limited, preferably a hydrophilic film obtained by polymerizing an amine compound or an acid group, and the amine compound having an amine group or an acid group is preferably It is acrylamide or isotonic acid; the invention may further comprise an amine-based amplifying agent layer on the light surface graft polymerization layer to increase the amount of surface amine groups and improve the crosslinking effect of the biological substance, and the amine-based amplification agent The material to be used is not limited, and is preferably an organic compound having an amine group, and is preferably PEI (p〇lyethyleneimine). The crosslinking agent of the present invention is preferably glutaraldehyde. 20 1252919 [Embodiment] In order to enable the reviewing committee to better understand the technical contents of the present invention, a preferred embodiment of the present invention will be described below.
實施例一、電漿沈積之生物感測裝置 5 以QCM為基材，利用平台式電漿處理設備，使QCM 能完全與電漿氣體均勻接觸。處理步驟如下：首先抽真空 至50mtorr;再通入HMDSZ氣體至150mtorr;以30W電漿氣 氛處理1分鐘，進行沈積有機石夕薄膜，隨即固定2.5 wt°/〇戊 二醛（GA)交連劑於有機矽薄膜上，即可進一步固定一單股 10 核酸探針於其上，最後以glycine作為遮蔽劑，將未反應完 全之戊二_交連劑反應完畢，即可用於檢驗待測物。 將固定程序各個步驟分別檢測其頻率變化，結果如圖 1，電漿處理後偵測到之頻率為9998925Hz左右，加上一層 交連劑（GA)後測得9998875Hz左右，於固定上核酸探針 15 (probe)後，測得9998775 Hz左右，使用glycine遮蔽劑後測 得9998725 Hz左右，於最後檢測待測物（以PCR增幅後，與 探針具互補特性之核酸待測物）後所測得之頻率為9998625 Hz左右。 隨著表面薄膜上沈積之物質增加，所偵測到之頻率逐 20 漸下降，顯示利用電漿沈積法確實可以將核酸探針固定於 QCM表面，但固定量不大，因為所沈積之薄膜為疏水性高 分子，較難以跟水溶***連劑，如戊二酸等反應，因此下 一實施例即測試增加一親水性薄膜之效果。 25 實施例二、電漿沈積輔以接枝反應之生物感測層 1252919 將經過電漿沈積法（如實施例一所述）處理後之QCM 取出，於其表面上滴上10wt%AAm水溶液20u卜以1000W 之UV光照射15分鐘，使表面進行接枝聚合反應，取出後再 以蒸餾水清洗過夜，藉以除去表面均質聚合物 5 (Homopolmers)，待陰乾後隨即固定2.5wt%戊二酸交連劑於 表面，即可進一步固定一單股核酸探針於其上，最後以 glycine作為遮蔽劑，將未反應完全之戊二酸交連劑反應完 畢，即可用於檢驗。 將固定程序各個步驟分別檢測其頻率變化，結果如圖 10 2，電漿處理後偵測到之頻率為9998925Hz左右，在覆蓋上 一層接枝聚合層AAm後，測得頻率為9998700Hz左右，加 上一層交連劑（GA)後測得9998550Hz左右，於固定上核酸 探針（probe)後，測得9998400Hz左右，使用glycine遮蔽劑 後測得9998350Hz左右，於最後檢測待測物（以PCR增幅後 15 之核酸待測物）後所測得之頻率為9998 150Hz左右。 隨著表面薄膜上沈積之物質增加，所偵測到之頻率逐 漸下降，且測得之頻率顯示經過電漿沈積後輔以UV光表面 接枝反應後形成之親水性薄膜，確實可提高核酸探針固定 於QCM表面的量。 20 實施例三、電漿沈積法與UV接枝反應後輔以添加層之生物 感測層 為使QCM表面胺基含量增加以提高交連劑作用，本實 施例於QCM進行電漿沈積與UV接枝聚合反應後，再利用 25 PEI (polyethyleneimine)作為胺基擴增劑固定於表面，以增 1252919 加胺基含量。方法為：再以AAm處理後之QCM表面滴上 4wt%PEI水溶液20ul，使反應一小時，隨後以蒸餾水清洗 並陰乾，再固定2.5wt%戊二醛交連劑於表面，並進一步固 定一單股核酸探針於其上，最後以glycine作為遮蔽劑，將 5 未反應完全之戊二醛交連劑反應完畢，即可用於檢驗。 將固定程序各個步驟分別檢測其頻率變化，結果如圖 3，在覆蓋上一層接枝聚合層AAm後，測得頻率為 9998700Hz左右，增加一層PEI後測得9998400Hz左右，加 上一層交連劑（GA)後測得9998300Hz左右，於固定上核酸 10 探針（probe)後，測得9998 100Hz左右，使用glycine遮蔽劑 後測得9998000Hz左右，於最後檢測待測物（以PCR增幅後 之核酸待測物）後所測得之頻率為9997700Hz左右。 由結果圖可發現以本實施例方法所製備出之生物感測 層可固定比實施例一、二更多之核酸探針分子，顯示經由 15 含胺基之PEI胺基擴增劑擴增處理後，可實際擴增表面胺基 量，增加與交連劑--戊二酸上酸基鍵結之量，而確實可因 交連劑的酸基增加，進而提高生物性分子之固定量。 實施例四、本發明與傳統探針固定法效果比較 20 將-SH與-biotin分子利用習知方法固定探針（核酸分子） 後，與本發明方法製備出之生物感測器進行比較，分別將 不同之生物感測層與PCR待測物進行核酸間之雜合反應 後，測試頻率之變化。 結果如圖4，圖上標示之-NH probe即代表本發明經由 25 實施例三所製備出之生物感測器。圖4中黑色長條為探針固 11 1252919 定後之頻率變化量，利用-SH probe固定核酸探針（圖中之 -SH olig〇nucle〇tide probe)後測得之頻率降低了 124Hz， -biotin 為 117Hz(圖中之-biotin olig0nucieotide pr〇be)，本發 明實施例4之-NH probe為177Hz(圖中之-amine 5 〇hg〇nucleotide probe)，顯示經由本發明實施例4所製備出 之生物感測裝置所能固定之探針分子量高於傳統之探針固 定法。 圖4中斜線長條所代表的是與待測物作用後之頻率改 變量，由圖4也可看出因本發明實施例4(圖中之-ami加 10 olig⑽ucleotide probe)所製備出之生物感測裝置所能固定 之探針分子量高，因此所能雜合到待測物之量亦較傳統固 定法為高。 實施例五、本發明生物感測裝置測試 15 本發明生物感測裝置製備完成後，與待測物進行雜合 反應之過程，利用液態流動方式即時偵測其雜合情形，結 果如圖5所示，由圖可看出待測物加入後（圖上之dna mjectum)，經過40分鐘之後，頻率變化即達穩定，顯示雜 合反應接近完成，也代表使用本發明生物感測裝置在實際 20檢測標的物時，只需要40分鐘，確實比傳統方法快速:不 而在靈敏度的測試上，從圖6a可以看出， 之待測物， ’只要 86ng/mlEmbodiment 1 Bio-sensing device for plasma deposition 5 Using QCM as a substrate, a platform-type plasma processing device is used to make QCM completely in contact with plasma gas. The treatment steps are as follows: firstly, vacuuming to 50 mtorr; then introducing HMDSZ gas to 150 mtorr; treating in a 30 W plasma atmosphere for 1 minute, depositing an organic stone film, and then fixing 2.5 wt%/〇glutaraldehyde (GA) crosslinking agent On the organic germanium film, a single strand of 10 nucleic acid probes can be further immobilized thereon, and finally, glycine is used as a masking agent, and the unreacted complete pentamethylene-crosslinking agent is reacted, and the test object can be used for testing. The frequency changes were detected in each step of the fixed program. The result is shown in Fig. 1. The frequency detected after the plasma treatment is about 9998925 Hz, and a layer of cross-linking agent (GA) is added to measure about 9899875 Hz. After (probe), it was measured at about 9987775 Hz, and after measuring with glycine masking agent, it was measured at about 9987.25 Hz. After the final detection of the analyte (after PCR amplification, the nucleic acid analyte with complementary characteristics of the probe) was measured. The frequency is around 9998625 Hz. As the amount of material deposited on the surface film increases, the detected frequency gradually decreases from 20 to 20, indicating that the nucleic acid probe can be immobilized on the surface of the QCM by plasma deposition, but the amount of immobilization is not large because the deposited film is Hydrophobic polymers are more difficult to react with water-soluble crosslinking agents such as glutaric acid, so the next embodiment tests the effect of adding a hydrophilic film. 25 Example 2: Bio-sensing layer of plasma deposition assisted by grafting reaction 1252919 The QCM treated by the plasma deposition method (as described in the first embodiment) is taken out, and a 10 wt% AAm aqueous solution 20u is dropped on the surface thereof. After irradiating with 1000W of UV light for 15 minutes, the surface was subjected to graft polymerization, and then taken out and washed with distilled water overnight to remove surface homogeneous polymer 5 (Homopolmers), and then fixed with 2.5 wt% glutaric acid cross-linking agent after drying. On the surface, a single-stranded nucleic acid probe can be further immobilized thereon, and finally, glycine is used as a masking agent, and the unreacted glutaric acid cross-linking agent is completely reacted, and can be used for the test. The frequency of each step of the fixed program is detected separately. The result is shown in Fig. 10 2. The frequency detected after the plasma treatment is about 9998925 Hz. After covering the upper layer of the graft polymerization layer AAm, the measured frequency is about 9998700 Hz, plus A layer of cross-linking agent (GA) measured about 9998550 Hz. After fixing the nucleic acid probe (probe), it measured about 9988400 Hz, and after using the glycine masking agent, it measured about 99,083,050 Hz. At the end, the test object was detected (after PCR amplification) The frequency measured after the nucleic acid test object is about 9998 150 Hz. As the substance deposited on the surface film increases, the detected frequency gradually decreases, and the measured frequency shows that after the plasma deposition, the hydrophilic film formed by the grafting reaction of the UV light surface can improve the nucleic acid detection. The amount by which the needle is attached to the surface of the QCM. 20 Example 3, the plasma deposition method and the UV grafting reaction, supplemented by the added layer of the biosensing layer, in order to increase the surface amine content of the QCM to enhance the effect of the crosslinking agent, the present embodiment is subjected to plasma deposition and UV bonding in QCM. After the polymerization of the branches, 25 PEI (polyethyleneimine) was used as an amine-based amplification agent to immobilize on the surface to increase the content of the amine group by 1252919. The method comprises the following steps: adding 20 ul of 4 wt% PEI aqueous solution to the surface of the QCM treated with AAm, allowing the reaction to be carried out for one hour, then washing with distilled water and drying it, fixing the 2.5 wt% glutaraldehyde cross-linking agent to the surface, and further fixing a single strand. The nucleic acid probe is applied thereto, and finally glycine is used as a masking agent, and the 5 unreacted glutaraldehyde cross-linking agent is completely reacted, and can be used for the test. The frequency changes were detected in each step of the fixed procedure. The result is shown in Fig. 3. After covering the upper layer of the graft polymerization layer AAm, the measured frequency is about 9998700 Hz, and after adding a layer of PEI, the measurement is about 9998400 Hz, plus a layer of cross-linking agent (GA). After the measurement of the nucleic acid 10 probe (probe), measured about 9998 100Hz, using the glycine masking agent measured 9998000Hz or so, the final detection of the test substance (by PCR amplification of the nucleic acid to be tested The frequency measured after the object is about 9997700 Hz. From the results, it can be found that the biosensing layer prepared by the method of the present embodiment can fix more nucleic acid probe molecules than the first and second examples, and shows that the PEI amine-based amplification agent containing 15 amine groups is amplified. After that, the amount of the surface amine group can be actually amplified, and the amount of the acid group bonded to the crosslinking agent-glutaric acid can be increased, and the acid group of the crosslinking agent can be increased, thereby increasing the fixed amount of the biological molecule. Example 4: Comparison of the effect of the present invention and the conventional probe immobilization method 20 After the probe (nucleic acid molecule) is immobilized by the -SH and -biotin molecules by a conventional method, the biosensor prepared by the method of the present invention is compared, respectively After the different biosensing layers and the PCR analyte are subjected to a heterozygous reaction between nucleic acids, the frequency is changed. The result is shown in Fig. 4. The NH probe indicated on the drawing represents the biosensor prepared by the present invention via the second embodiment. In Fig. 4, the black strip is the frequency change after the probe solid 11 1252919 is fixed. The frequency measured by immobilizing the nucleic acid probe (-SH olig〇nucle〇tide probe) with -SH probe is reduced by 124 Hz, - The biotin is 117 Hz (biotin olig0nucieotide pr〇be in the figure), and the -NH probe of Example 4 of the present invention is 177 Hz (amine 5 〇hg〇nucleotide probe in the figure), which is shown to be prepared according to Example 4 of the present invention. The molecular weight of the probe that can be immobilized by the biosensing device is higher than that of the conventional probe immobilization method. The oblique line in Fig. 4 represents the amount of frequency change after the action with the object to be tested, and the organism prepared by the embodiment 4 of the present invention (the ami plus 10 olig (10) ucleotide probe) can also be seen from Fig. 4 The probe capable of being fixed by the sensing device has a high molecular weight, so that the amount of the analyte to be mixed is higher than that of the conventional fixing method. Embodiment 5 Test of Biosensing Device of the Invention 15 After the preparation of the biosensing device of the present invention, the heterozygous reaction is carried out by using a liquid flow method after the hybrid reaction with the test object, and the result is shown in FIG. 5 . It can be seen from the figure that after the test object is added (dna mjectum on the figure), after 40 minutes, the frequency change is stable, indicating that the hybrid reaction is nearly completed, and also represents the actual use of the biosensing device of the present invention. When the target is detected, it only takes 40 minutes, which is faster than the traditional method: not only in the sensitivity test, as can be seen from Fig. 6a, the object to be tested, 'as long as 86ng/ml
要到189ng/ml以上的濃度才能被偵測到（請參見圖讣) 變化，然而 12 1252919 實施例六、本發明生物感測裝置安定性測試 將經過不同程序處理後之QCM生物感測裝置置於室 溫乾燥箱及〇〇C冰箱中儲存20天，進行安定性測試，觀察頻 率的變化。圖7為經過電漿沈積處理（PD-HMDSZ)，UV光接 5 枝聚合 （PD-HMDSZ\g\AAm) ， PEI胺基擴增 (PD-HMDSZ\g\AAm\PEI) ， 交 連 劑 固 定 (PD-HMDSZ\g\AAm\PEI\GA)，核酸探針固定 (PD-HMDSZ\g\AAm\PEI\GA\probe)及 glycine 遮蔽處理 (PD-HMDSZ\g\AAm\PEI\GA\probe\glycine)後，置於室溫乾 10 燥箱之安定性測試，結果顯示QCM經不同處理於放置19天 後，尚有90%以上之安定性。 表一則顯示不同存放環境對本發明QCM生物感測裝 置安定性之影響，結果顯示存放於室溫乾燥箱中或冰箱 中對安定性之影響不大。 15 表一、本發明生物感測裝置安定性測試To be detected at a concentration above 189 ng/ml (see Figure 讣), however, 12 1252919 Example 6 The stability test of the biosensing device of the present invention will be processed by a QCM biosensing device after different procedures. Store in a dry box at room temperature and in a refrigerator for 20 days for stability testing to observe changes in frequency. Figure 7 shows plasma-deposited treatment (PD-HMDSZ), UV-lighted 5-band polymerization (PD-HMDSZ\g\AAm), PEI amine-based amplification (PD-HMDSZ\g\AAm\PEI), cross-linking agent fixation (PD-HMDSZ\g\AAm\PEI\GA), nucleic acid probe immobilization (PD-HMDSZ\g\AAm\PEI\GA\probe) and glycine masking treatment (PD-HMDSZ\g\AAm\PEI\GA\ After probe\glycine), the stability test was carried out in a dry box at room temperature. The results showed that QCM had more than 90% stability after being treated for 19 days. Table 1 shows the effect of different storage environments on the stability of the QCM biosensing device of the present invention. The results show that the storage in a room temperature oven or in the refrigerator has little effect on the stability. 15 Table 1, the stability test of the biosensing device of the present invention
Decay ratio {%) ..、— (fc ' —----- 25yC PH HMDSZ 97.4 >:.:V ........... ” 、 1 PD []MDSZ\^AAm ， 、 ........................................................................................................ .. Λ ^ 96,8 -- 92.6 ' ' PI) HN4DS7：^-AAnvFP,I 1........ 一二… 〜〜 93,3 〜...........-.........._j 92 1 ί PD HMDS/^AAn^PF7r<iA 9U) __ 一---..... 蚁3 ·6 ;hiMDS/e-AAnvma.Vpi'Gbe 94,6 ——__ 上述實施例僅係為了方便說明而舉例而已，本發日月戶斤 主張之權利範圍自應以申請專利範圍所述為準，而#IΜ 20 於上述實施例。 13 1252919 【圖式簡單說明】 圖1係本發明實施例一之各個固定程序之頻率變化 圖2係本發明實施例二之各個固定程序之頻率=化 5圖3係本發明實施例三之各個固定程序之又 竿變化 圖4係本發明與傳統之探針固定法效果比較圖。 圖5係本發明生物感測裝置反應時間表。回。 圖6a係本發明生物感測裝置靈敏度測試結果。 圖6b係傳統之電泳法靈敏度測試結果。 10圖7係本發明生物感測裝置安定性測試。 表係本發明生物感蜊裝置安定性測試。 【圖號說明】 4 14Decay ratio {%) .., — (fc ' —----- 25yC PH HMDSZ 97.4 >:.:V ........... ” , 1 PD []MDSZ\^AAm , , ................................................. .................................................. ..... .. Λ ^ 96,8 -- 92.6 ' 'PI) HN4DS7: ^-AAnvFP, I 1........ One two... ~~ 93,3 ~... .....-.........._j 92 1 ί PD HMDS/^AAn^PF7r<iA 9U) __ one---..... ant 3 ·6 ;hiMDS/e- AAnvma.Vpi'Gbe 94,6 ——__ The above embodiments are only examples for convenience of explanation, and the scope of rights claimed by this syllabus shall be subject to the scope of the patent application, and #IΜ 20 13 1252919 BRIEF DESCRIPTION OF THE DRAWINGS FIG. 1 is a frequency change of each fixed program according to Embodiment 1 of the present invention. FIG. 2 is a frequency of each fixed program according to Embodiment 2 of the present invention. FIG. 3 is an embodiment of the present invention. Fig. 4 is a comparison of the effects of the present invention and the conventional probe fixing method. Fig. 5 is a reaction schedule of the biosensing device of the present invention. Fig. 6a is the sensitivity of the biosensing device of the present invention. Test results. Figure 6b is the result of the traditional electrophoresis sensitivity test. Figure 7 is the stability test of the biosensing device of the present invention. The table is the stability test of the biosensing device of the present invention. [Description of the figure] 4 14