200841011 九、發明說明： 【發明所屬之技術領域】 本發明是有關於-種介電泳晶片，特別是指—種具微粒 分離與捕捉濃縮功能之介電泳晶片。 【先前技術】 、在床核驗與一般食品檢驗方面，都希望能夠以最快 . 冑：確的方式檢測出檢體所含的細菌種類或特定生物微粒 • ，以方便掌控抗生素之使用時機與種類。在細菌捕捉 ^ 濃縮方面，由於檢體中某些需要檢測的細菌濃度通當非當 的/，她。一如此稀少的細菌濃 檢測鑑定的，而且細菌是呈現散亂的分佈在懸浮液中，容 易因布朗運動或自身鞭毛的擾動而無法固定其位置，傳統 方法是以培養的方式，先將檢體中的細菌培養至一定濃度 、，一般濃度大約需要至1〇M〇8cFU/ml，核較有效的被檢 測出來，經過陪養的程序一般約須經過24〜48小時，有此 • 生長緩慢之細菌甚至須經數天的時間培養才有辦法長到足 夠的濃度，如幽門桿菌約需耗費四到七天的時間。如此耗 時且繁雜的過程，對於一些因微生物感染之急症，往往緩 ， 不濟急，無法符合臨床上的需要，若檢體中之細菌種類不 ‘ /、一種時，則得花更多時間進行不同菌種的分離與培養。 雖然目W已有許多不同類型之介電泳晶片，但大部分 都疋採用無流體流動之濃縮方式，以四極式電極介電泳晶 片為例，粒子可被負介電泳力捕捉於四電極中間，但由於 電场強度會隨著離電極表面越遠而越衰減，故捕捉濃縮效 5 200841011 果並不佳’若有流體條件則懸浮於較上方的粒子將無法受 到有效的介電泳力操控’且此捕捉方式電麗—開啟後就無 法有更多的粒子進入，低濃度的檢體較無法以此方式進行 濃縮，且無法以捕捉面積進行濃度定量。 【發明内容】 因此，本發明之目的，即在提供一種可捕捉濃縮一介電 泳液中具不同介電特性之微粒的介電泳晶片。200841011 IX. DESCRIPTION OF THE INVENTION: TECHNICAL FIELD OF THE INVENTION The present invention relates to a dielectrophoretic wafer, and more particularly to a dielectrophoretic wafer having a particle separation and capture concentration function. [Previous technology] In terms of bed verification and general food inspection, it is hoped that the bacteria type or specific biological particles contained in the sample can be detected in the fastest way: in order to control the timing and type of antibiotics. . In terms of bacterial capture ^ concentration, due to the concentration of certain bacteria in the sample that needs to be detected improperly, she. A rare bacterial concentration test identified, and the bacteria are scattered in the suspension, easy to fix their position due to Brownian motion or self-flagellation. The traditional method is to cultivate the sample first. The bacteria in the medium are cultured to a certain concentration, and the general concentration is about 1〇M〇8cFU/ml. The nuclear is more effectively detected. After the accompanying procedure, it usually takes about 24 to 48 hours, and the growth is slow. It takes even a few days for the bacteria to grow until there is enough concentration. For example, Helicobacter pylori takes about four to seven days. Such a time-consuming and complicated process is often slow and inconvenient for some acute diseases caused by microbial infections, and cannot meet the clinical needs. If the bacteria in the sample are not '/, one type, then it takes more time. Isolation and culture of different strains. Although there are many different types of dielectrophoresis wafers, most of them use a fluid-free flow concentration method. For example, a quadrupole electrode dielectrophoresis wafer can be captured by a negative dielectrophoretic force in the middle of the four electrodes. Since the electric field strength is attenuated as it is farther away from the electrode surface, the capture concentration effect 5 200841011 is not good. If there is a fluid condition, the particles suspended above the upper one will not be manipulated by the effective dielectrophoretic force. Capturing mode is not possible. After opening, there is no more particles to enter. Low-concentration samples are less concentrated in this way, and concentration cannot be quantified by the capture area. SUMMARY OF THE INVENTION Accordingly, it is an object of the present invention to provide a dielectrophoretic wafer that captures particles having different dielectric properties in a concentrated liquid bath.
本發明之另-目的’在於提供—種可分離與捕捉濃縮一 介電泳液中具不同介電特性之微粒的介電泳晶片。 於是，本發明具捕捉濃縮功能之介電泳晶片，適用於捕 捉一介電泳液中具特定介電特性的微粒，並包含上、下間 隔相向之-上基板與-下基板、—疊接於該等基板相向側 面間之流道成型層，及二上下間隔對稱地分別被覆固定於 該等基板相向側面之電極層。該流道成型層與該等基板相 配合界定出-左右延伸而可供介電泳液流動之中空微流道 。該等電極層分別包括-前後延伸之捕提電極，且該等捕 捉電極分別具有一横越微流道且呈開口迎向流經之介電泳 液的v㈣第-捕捉部，且#料捕捉電極被施加預定頻 率之交流電時，該等第一插扣加1 ^ 捕捉4可將通過之介電泳液中具 特定介電特性的微粒捕捉擋下。 【實施方式】 、有關本發明之前述及其他技術内容、特點與功效，在 以下配合參考圖式之一個輕私给 清料H a例的詳細說明中，將可 200841011 S片:圖卜2所示’本發明具分離與捕捉濃縮功能之介電泳 較佳實施例·，適用於將介電泳液中的具有不同介電特性 二、目未710進仃分離與捕捉濃縮，該介電泳可以是-般 =或是真正檢體製叙溶液，例如稀釋後之血液、尿液、牛 : 該W粒可以是非峰必7妈f点丨L 〇33 物微粒（例如乳膠微粒），或是生物微 粒（例如細胞、血球、細菌或酵母菌…等）。 該介電泳晶片包含上下間隔平行之—上基板3盘_下 基板4、-疊接於該等基板3、4之相向側面間之流道成型 反5，及二上下間隔對稱地分別被覆固定於該等基板3、* 相向側面之電極層6。 士該等基板3、4是由玻璃板（glass slide)製成，但實施 ^亦可視需求由石英或矽基材製成。其中，上基板3具 有一貫穿其左端部之注液孔301，及前、後間隔地分別貫穿 其右端部之-第-與-第二排液孔302、3〇3。該流道成型 板5是由SU8製成，且與疊接於其頂、底面之該等基板3 、4相配合界定出一左右延伸而可供介電泳液流動之中空微 流迢50。該微流道5〇具有一左右延伸且左端與該注液孔 3〇1連通之主流段501，及前、後間隔且分別與主流段5〇ι 連通地自主流段501右端往右延伸之一第一與一第二分流 段502、503，且該等分流段502、5〇3右端是分別與該等排 液孔302、303對應連通。但實施時，該等基板3、4與流 道成型板5之材質皆不以上述材料為限。 在本貫施例中，該微流道5 0之主流段5 〇 1寬丨m ， Μ πι，高約 高25 // m，而該等分流段502、503寬約350 7 200841011 但實施時’微流道5Q結構比例不以此為限。 該等電極層6是由導電金屬材料製成，且呈薄膜狀， 分別具有由左至右依序排列之—第—分選電極61、—第二 分選電極62,及一捕捉電極63。該等第一分選電極‘分 別具有-自主流段5G1前側邊往右後方水平延伸入主流段 中之第77選部611，該等第二分選電極62分別具有一 i主流段5()1後側邊對應位於第—分選部611末端處，往右 • 丽方水平延伸入主流段501中之第二分選部62卜且該等第 - 二分選部621末端是位於第一分流段502中。 該等捕捉電極63是前後彎折延伸地橫越該等分流段 5〇2二503，分別具有橫越該等分流段繼、5〇3之一第一及 一第二捕捉部631、634，該等捕捉部631、州大致呈開口 朝向所對應分流段502、5〇3與主流段5〇1連通處之v字型 丄亦即該等捕捉部631、634開口是迎向來自主流段3〇1之 介電泳液。該等捕捉部叫634)皆具有二分別往右相向 • 傾斜沿伸入相對應分流段502 (503)中之平直導引段632 (幻5 )，及二分別自該等導引段《2 ( 635)末端以一預定 曲率往右相向傾斜弧彎延伸且末端連接在—起之捕捉段㈣ )且忒等捕捉段633 ( 636 )連接處是位於相對應分 - 流段502 ( 503)中間區域。 透過該等上、下間隔對稱之捕捉部ό31、634的導引段 632、^635與捕捉段奶、636所構成之v字型的結構設計， :先藉由該等導引段632、635產生之負介電泳力，將快速 動之；1電永液中的微粒擋下，而無法通過該等上下間隔 8 200841011 之導引段632、635間的空間，並可將被擋下之微粒逐漸導 引至該等弧彎狀捕捉段633、635，而使該等微粒位移速度 逐漸減慢，且因該等捕捉段633、635相連接之尖端處會二 應產生最強之電場效應，因而可形成大於介電泳液之流體 作用力的強負介電泳力，使被導引至該等捕捉段633、635 間的微粒，可被該強負介電泳力作用而無法通過該等上下Another object of the present invention is to provide a dielectrophoretic wafer that can separate and capture particles having different dielectric properties in a concentrated electrophoretic fluid. Therefore, the present invention has a digesting function-capable dielectrophoresis wafer, which is suitable for capturing particles having a specific dielectric property in a dielectrophoresis liquid, and includes upper and lower spacers facing the upper substrate and the lower substrate, and being stacked thereon. The flow channel forming layer between the opposite side faces of the substrate and the electrode layers on the opposite side faces of the substrates are respectively covered and symmetrical. The flow channel forming layer cooperates with the substrates to define a hollow microchannel extending to the left and right for the flow of the dielectrophoretic liquid. Each of the electrode layers includes a front-and-left extending extraction electrode, and each of the capture electrodes has a v(four) first-capture portion that traverses the micro-flow channel and faces the dielectrophoretic liquid flowing through the opening, and the #-capture electrode is When a predetermined frequency of alternating current is applied, the first buckle plus 1 ^ capture 4 captures the particles having specific dielectric properties in the passing dielectrophoresis fluid. [Embodiment] In relation to the foregoing and other technical contents, features and effects of the present invention, in the following detailed description of a light private cleaning material H a with reference to the reference pattern, the 200841011 S piece: Figure 2 The present invention is a preferred embodiment of the dielectrophoresis with separation and capture concentration function of the present invention. It is suitable for separating and capturing and enriching the dielectrophoresis solution with different dielectric properties. The dielectrophoresis can be - Or = true test system solution, such as diluted blood, urine, cattle: The W grain can be non-peak must be 7 f f 丨 L 〇 33 particles (such as latex particles), or biological particles (such as Cells, blood cells, bacteria or yeast...etc.). The dielectrophoresis wafer comprises a vertical substrate 3 parallel to the upper substrate 3, a lower substrate 4, a flow channel forming reverse 5 laminated between opposite sides of the substrates 3, 4, and the upper and lower symmetrical layers are respectively fixed and fixed The substrate 3, * the electrode layer 6 facing the side. The substrates 3, 4 are made of glass slides, but can be made of quartz or tantalum substrates as desired. The upper substrate 3 has a liquid injection hole 301 penetrating through the left end portion thereof, and the first and second liquid discharge holes 302, 3, 3 are respectively inserted through the right end portion of the front and rear portions. The flow path forming plate 5 is made of SU8 and cooperates with the substrates 3 and 4 which are superposed on the top and bottom surfaces thereof to define a hollow micro-flow 50 which is left and right for the flow of the dielectrophoretic liquid. The microchannel 5 has a main flow section 501 extending left and right and communicating with the liquid injection hole 3〇1 at the left end, and the right end of the autonomous flow section 501 extending to the right and the front and rear intervals and communicating with the main flow section 5〇, respectively. A first and a second splitter section 502, 503, and the right ends of the splitter sections 502, 5〇3 are respectively in communication with the drain holes 302, 303. However, in the implementation, the materials of the substrates 3, 4 and the flow channel forming plate 5 are not limited to the above materials. In the present embodiment, the main section 5 〇1 of the microchannel 50 is wider than m, Μ πι, and the height is about 25 // m, and the sections 502 and 503 are about 350 7 200841011. The microfluidic 5Q structure ratio is not limited to this. The electrode layers 6 are made of a conductive metal material and are in the form of a film having a first-sorting electrode 61, a second sorting electrode 62, and a trapping electrode 63 arranged in order from left to right. The first sorting electrodes ' respectively have a front side of the autonomous flow segment 5G1 extending horizontally to the right rear into the 77th selection portion 611 of the main flow segment, and the second sorting electrodes 62 respectively have an i main flow segment 5 ( 1) the rear side corresponds to the end of the first sorting unit 611, and the right side • the horizontal side extends horizontally into the second sorting unit 62 of the main stream section 501, and the end of the second-stage sorting unit 621 is located at the first In the split section 502. The capture electrodes 63 are bent forward and backward across the splitter segments 5〇2 and 503, respectively having one of the first and second capture portions 631, 634 crossing the splitter segments, 5〇3, respectively. The capturing portions 631 and the states are substantially v-shaped with the openings facing the corresponding shunt segments 502, 5〇3 and the main stream segments 5〇1, that is, the openings of the capturing portions 631 and 634 are welcoming from the main stream segment 3 〇 1 Dielectrophoresis solution. The capture portions are 634) each having two rightward facing directions, a slanting edge extending into the corresponding splitting section 502 (503), and a second guiding segment 632 (magic 5), and two from the guiding segments respectively 2 ( 635) end with a predetermined curvature extending to the right oblique arc and the end is connected to the catching segment (4)) and the connecting portion of the capturing segment 633 ( 636 ) is located at the corresponding sub-flow segment 502 ( 503) Middle area. The v-shaped structural design formed by the guiding sections 632, 635 and the capturing section milk 636 of the capturing sections 31, 634 of the upper and lower spacing symmetry: firstly by the guiding sections 632, 635 The negative dielectrophoretic force generated will be rapidly moving; the particles in the electro-permanent liquid are blocked, and the space between the guiding segments 632 and 635 of the upper and lower intervals 8 200841011 cannot be passed, and the particles to be blocked can be removed. Gradually guiding to the arc-shaped trapping segments 633, 635, the displacement speed of the particles is gradually slowed down, and the strongest electric field effect is generated at the tip end of the connecting segments 633, 635. Forming a strong negative dielectrophoretic force greater than the fluid force of the dielectrophoretic fluid, so that the particles guided between the capture segments 633, 635 can be subjected to the strong negative dielectrophoretic force and cannot pass through the upper and lower
間隔之捕捉段633、635間的空間，而逐漸被限位聚集於該 專捕捉段6 3 3、6 3 5左侧。 為使該等捕捉段633、636可有效捕捉微粒，該等相連 接之捕捉段633、636之較佳夹角（0)範圍介於4〇。〜45 ，該等捕捉段633、636之弧彎曲率定義為：每一捕捉段 左、右端之前後間距⑴與左右間距⑷的比值，本： 明可實施之曲率範圍小於等於i，但較佳之曲率範圍則小: 等於0.5,在本實施例以下說明中，該等捕捉段阳、伽 曲率為0.45，該等相連接之捕捉段633、㈣夾角則為 叮疋上述較佳曲率範圍（ 米斗斤 受亏1，是因為 心專捕捉段633、636曲率範圍介於OH時，雖麸 ^段⑶、㈣仍可產生捕捉微粒之介電泳力，但^因 以寺捕捉段633、636之曲率角度變化太快，而造成介 液流動時所產生之流體作用力大於該等捕捉段633、636之 力，而降低該等捕捉段633，有效捕捉操控微 /效率’針對曲率大於G_5的外型結構將於後另述。 當要以該介電泳晶片分離介電泳液中之不同微粒時， 9 200841011 可先於該等電極層6之該等分選電極61、62與捕捉電極幻 施加不同頻率之交流電，使該等分選電極61、62與捕捉電 ，63可分別對不同之微粒產生強度差異的負介電泳力。接 者’便可將具有不同介電特性之微粒的介電泳液自上基板3 之注液孔301逐漸注入微流道5〇中，便可開始進行微粒之 分選與捕捉濃縮。並可搭配其它檢測儀器（圖未示），例如 拉曼光譜與儀影像擷取器等，進行定性與定量檢測。 φ 配合圖3、4所示，首先針對該等分選電極61、62之 - 作用進行說明，以經稀釋後之血液檢體中的紅血球與腸球 菌（五· )進行分選測試，其中，於該等第一分選電 極施加電訊號為20VP_P，400 kHz，而於該等第二分選電極施 家電訊號為10VP_P，400 kHz，檢體於微流道5〇中之流速為 200 μπι/sec。當紅血球與腸球菌被流動之介電泳液帶向該等 第一分選電極時，該等第一分選電極61對紅血球與腸球菌 產生之負介電泳力會大於介電泳液之流體作用力，使得此 φ 兩種生物微粒接無法通過該等第一分選部間的區域，而一 起沿該第一分選部611延伸方向逐漸位移至主流段5〇1後側 邊，而流向第二分選電極62。 - §鄰近主流段501後侧邊之紅血球與腸球菌被導引至 - 第二分選電極62時，在上述交流電訊號條件下，第二分選 電極對於紅血球所產生負介電泳力會大於流體作用力，所 以紅血球會被該等第二分選部621排斥，而沿第二分選部 621延伸方向位移進入第一分流段5〇2中。該等第二分選電 極對於腸球菌所產生之負介電泳力較流體作用力弱，所以 10 200841011 在上述介電泳液流速作用下’腸球菌會直接被介電泳液帶 動而沿著主流段501後侧邊通過該等第二分選電極62，而 依序進入第二分流段503中，進而可將該等不同介電特性 之生物微粒分別導引至不同的分流段502、503中，而達到 分選之目的。 配合圖5、6，以下繼續說明該等捕捉電極63位於該等 为仙·段502、503之捕捉部631、634的捕捉濃縮作用。 繼續以上述紅血球及腸球菌為例，該等捕捉電極分別 被施加之電訊號為20Vp-P，500 kHz，此時’該等捕捉部對於The space between the segments 633 and 635 is captured by the interval, and is gradually limited by the limit on the left side of the dedicated capture segment 6 3 3, 6 3 5 . In order for the capture segments 633, 636 to effectively capture particles, the preferred included angles (0) of the connected capture segments 633, 636 range from 4 〇. 〜45, the arc bending rate of the capturing segments 633, 636 is defined as: the ratio of the front and rear spacing (1) to the left and right spacing (4) of the left and right ends of each capturing segment, and the curvature range that can be implemented is less than or equal to i, but preferably The range of curvature is small: equal to 0.5. In the following description of the embodiment, the capture section has a positive and gamma curvature of 0.45, and the angles of the captured segments 633 and (4) are the preferred curvature ranges. Jin suffered a loss of 1, because the heart-shaped capture section 633, 636 curvature range is between OH, although the bran section (3), (four) can still produce the dielectrophoretic force of capturing particles, but ^ because of the curvature of the temple capture section 633, 636 The angle changes too fast, and the fluid force generated when the liquid flows is greater than the force of the capturing segments 633, 636, and the capturing segments 633 are lowered, effectively capturing the manipulation micro/efficiency 'for the shape with curvature greater than G_5 The structure will be described later. When the different particles in the dielectrophoresis liquid are to be separated by the dielectrophoretic wafer, 9 200841011 may apply different frequencies to the capture electrodes 61 and 62 of the electrode layers 6 and the capture electrodes. AC power to make such sorting The electrodes 61, 62 and the trapping electrodes 63 can respectively generate a negative dielectrophoretic force for the difference in intensity of the different particles. The carrier can then pass the dielectrophoretic solution of the particles having different dielectric properties from the liquid injection hole 301 of the upper substrate 3. Gradually inject into the microchannel 5〇, you can start the sorting and capture concentration of the particles, and can be used for qualitative and quantitative detection with other detection instruments (not shown), such as Raman spectroscopy and image picker. φ, as shown in Figs. 3 and 4, firstly, the action of the sorting electrodes 61 and 62 is described, and the red blood cells and the enterococci (five) in the diluted blood sample are subjected to sorting test, wherein The first sorting electrodes are applied with an electrical signal of 20 VP_P, 400 kHz, and the second sorting electrodes are applied with a home signal of 10 VP_P, 400 kHz, and the flow rate of the sample in the micro flow channel 5 为 is 200 μπι/ When the red blood cells and enterococci are carried to the first sorting electrodes by the flowing dielectrophoresis liquid, the first sorting electrode 61 generates a negative dielectrophoretic force for the red blood cells and the enterococci which is greater than the fluid of the dielectrophoresis liquid. Force, making this φ two The particles are not able to pass through the regions between the first sorting portions, and are gradually displaced along the extending direction of the first sorting portion 611 to the rear side of the main stream segment 5〇1, and flow to the second sorting electrode 62. § When the red blood cells and enterococci adjacent to the back side of the mainstream segment 501 are guided to the second sorting electrode 62, under the above-mentioned alternating current signal condition, the second sorting electrode will generate a negative dielectrophoretic force for the red blood cells to be greater than the fluid effect. The force, so the red blood cells are repelled by the second sorting portion 621, and are displaced into the first splitting portion 5〇2 along the extending direction of the second sorting portion 621. The second sorting electrodes are generated for the enterococci The negative dielectrophoretic force is weaker than the fluid force, so 10 200841011 Under the action of the above-mentioned dielectrophoretic fluid flow rate, the enterococci will be directly driven by the dielectrophoresis liquid and pass through the second sorting electrode 62 along the rear side of the main flow section 501. And sequentially entering the second splitting section 503, and then the biological particles of different dielectric properties can be respectively guided to different splitting sections 502, 503 to achieve the purpose of sorting. 5 and 6, the capture and concentration of the capture electrodes 63 located in the capture portions 631 and 634 of the segments 502 and 503 will be further described below. Taking the above red blood cells and enterococci as an example, the electric signals applied to the capture electrodes are respectively 20Vp-P, 500 kHz, at which time the capture portions are
該等紅血球與腸球菌所產生之負介電泳皆大於流體作用力 ’所以上述紅血球與腸球菌分別被分選至第一與第二分漭 段後，會分別被該等捕捉部之負介€泳力排彳，而無= 過捕捉部間的空間，並在介電泳液的帶動下，逐漸地分別 聚集限位於該等捕捉部左側，而完成紅血球與長 捉濃縮。 丹以生乳為例，將生乳進行 ^ 0么"毛* 曰曰月 將生乳中之較大體細胞與較小之細菌分選至該等分流段地 、5〇3後’再將該等體細胞與細菌分別捕捉濃縮於該 部⑶、㈣左側。當以不同之生乳稀釋倍數（1〇〇 = :0捕：^測試時，可發現所捕捉濃縮之細菌的堆積面積 二％間間具有相對應之線性關係，兩者之捕捉倍率介 於2〜2·2間，如圖7所示。 而相同稀釋倍率之生朝名 飨眭女 生礼在不同流速情況下進行捕捉濃 、-¥，亦可發現流速盥捕 〃補捉之細函堆積面積間亦具有 11 200841011 之線性關係，如圖8所示。 在完成上述之生物微粒的分選與捕捉濃縮後，由於生 物微粒接集中於該等捕捉部63 i、634左側，因此，可以其 它儀器進行定性與定量，例如以拉曼光譜儀測定該等被捕 捉'/辰縮之生物微粒種類，由於不同種類之生物微粒會具有 不同之拉曼光譜訊號，所以可藉由拉曼光譜儀所測定之訊 號差異，鑑定出所捕捉濃縮之生物微粒種類，如圖9所示The negative dielectrophoresis generated by the red blood cells and enterococci is greater than the fluid force'. Therefore, after the red blood cells and enterococci are sorted to the first and second branching stages, respectively, they are respectively negatively affected by the capturing parts. The swimming force is drained, and there is no space between the capturing portions, and under the driving of the dielectrophoresis liquid, the concentration limits are gradually located on the left side of the capturing portions, and the red blood cells and the long-concentration are completed. Dan takes raw milk as an example, and the raw milk is subjected to ^0?"Mao* 曰曰月. The larger somatic cells and smaller bacteria in the raw milk are sorted to the same segment, after 5〇3, then the body The cells and bacteria are separately concentrated and concentrated on the left side of the parts (3) and (4). When different dilutions of raw milk (1〇〇=:0 catch: ^ test, it can be found that there is a corresponding linear relationship between the two% of the accumulated area of the captured concentrated bacteria, the capture ratio of the two is between 2~ 2·2, as shown in Figure 7. And the same dilution rate of the students of the famous 飨眭 在 在 at different flow rates to capture the concentration, - ¥, can also find the flow rate 盥 〃 〃 之 之 之 之 细 细It also has a linear relationship of 11 200841011, as shown in Fig. 8. After the sorting and capturing concentration of the above-mentioned biological particles is completed, since the biological particles are concentrated on the left side of the capturing portions 63 i, 634, other instruments can be performed. Qualitative and quantitative, for example, the Raman spectrometer is used to determine the type of captured biological particles. Since different kinds of biological particles will have different Raman spectral signals, the signal difference can be measured by Raman spectrometer. , identifying the type of concentrated biological particles captured, as shown in Figure 9.
以拉叉光瑨儀測定該介電泳晶片所捕捉濃縮之大腸桿菌 (反C〇//)與乳桿菌（kdM此沿⑽）時，兩者所得到之拉 曼=譜訊號具有明顯之差異性，可證實此介電泳晶片之捕 捉迅極63所產生之捕捉與濃縮效果，確實可幫助拉曼光譜 儀進行連續流體下之偵測。 /當生物微粒之種類確定後，便可以影像擷取器，例如 攝影機或照相機，操取被該等捕捉部631、634捕捉濃縮之 生物微粒影像’並經由影像分析設備（圖未示）之處理， ==微流道50高度、所擷取之微粒聚集面積與單—微粒 茶數，而計算出總捕捉微粒數量，然後，再依據單 1=之介電泳液流量與捕捉所花費時間等參數，而計算 出^體的總微粒濃度。 的；由：ΓΓ月之介電泳晶片與上述檢測設備-起使用 :’可快逮且有效地分析出檢體中之細 :斤：可大幅縮短食品或醫療檢體之檢驗分析'純化菌 種培養鑑定與定量所發費之 沭化、囷 I, ^ ^ ± t間，在醫療檢測方面，可使 w療人貝快速得知病人症狀與病因，而可即時的給藥與： 12 200841011 療，在食品檢測方面， 細菌、酵母菌等）、總量；類件知食品中所含之微生物（ 管理品質。但實施時，=八币，而可有效提高食品檢測與 粒的定性盘$旦t $ tb δΛ i'永aa片所捕捉濃縮之生物微 -、疋里万法皆不以p 學檢:P1八k # 上这方法為限，亦可透過電化 ..氕石進仃定性與定量。由於上述 述。 並非本务明創作重點，因此不再詳When the concentrated electrophoresis of Escherichia coli (anti-C〇//) and Lactobacillus (kdM) (10) were measured by a cross-hatch photometer, the Raman=spectrum signals obtained by the two were significantly different. It can be confirmed that the capture and concentration effect generated by the capture of the dielectrophoretic wafer 63 can indeed help the Raman spectrometer to detect under continuous fluid. / When the type of the biological particles is determined, the image capturing device, such as a camera or a camera, can be used to capture the concentrated biological particle image 'by the capturing portions 631 and 634 and processed by the image analyzing device (not shown). , == the height of the microchannel 50, the area of the particles collected and the number of single-particle teas, and calculate the total number of particles captured, and then according to the parameters of the flow rate of the dielectrophoresis solution and the time taken for capturing. And calculate the total particle concentration of the body. By: Haoyue Dielectrophoresis Wafer and the above-mentioned testing equipment - use: 'Quickly and effectively analyze the fineness of the specimen: Jin: can greatly shorten the inspection analysis of food or medical specimens' purified strains In the case of medical identification and 定量I, ^ ^ ± t, in the medical testing, the patient can quickly learn the symptoms and causes of the patient, and can be immediately administered with: 12 200841011 In terms of food testing, bacteria, yeast, etc., the total amount; the micro-organisms contained in the foods (management quality. But when implemented, = eight coins, which can effectively improve the quality of food testing and grain t $ tb δΛ i' Yong Aa film captures the concentrated micro--, 疋里万法不在p学检: P1八k# This method is limited to, but also through the electrification. Quantitative. Because of the above, it is not the focus of this work, so it is no longer detailed.
如圖10、11所示，各 田通寺捕捉部631、634的該等捕捉 丰又633、636弧彎曲率大於〇车 。 t % & υ·5犄，例如設計成圖10所示之 圓弧型時，曲率為丨，料捕捉段633(636)產生之負介 電泳力《可用以捕捉濃縮微粒，如圖u所示（生物微粒 酵母菌（a/wca似》，但經實際測試，其捕捉效率 會較前述捕捉段633、636所構成字型結構差。 另外，在本實施例中，該介電泳晶片之微流道5Q僅具 有一分流段502、503，而該等電極層6亦僅設置二左、右 間隔之分選電極61、62，但實施時，該等分流道5〇2、5〇3 之數量可依要分選之微粒種類數量而增加，並可對應增加 突伸入微流道50中的分選電極61、62數量與捕捉電極63 之捕捉部631、634數量，使多種不同介電特性之微粒在介 電泳液流動過程中，逐漸被分選至預定之分流段501、502 中並被分別捕捉濃縮，但實施時不以此為限。 歸納上述，透過該等分選電極61、62與捕捉電極63 之結構設計，使得本發明介電泳晶片可快速地將介電泳液 中具有不同介電特性之微粒分離並導引至預定區域，並藉 13 200841011 由該等捕捉電極63之捕捉部631、634的結構設計，而有 f也將被刀選出之微粒捕捉聚集在一固定區域，以方便後 疋〖生/、疋里檢測。當該介電泳晶片應用於食品或醫療 U之生物微粒檢測時’可快速地將檢體中之各種微量生 物㈣分離與捕捉聚集，進而節省大量微生物培養、純化 菌種釔定與定里所發費之時間，使得食品檢驗人員或醫 療人員可快速進行微生物定性與定量。因&，確實可達到 本發明之目的。As shown in Figs. 10 and 11, the capture ratios of the 633 and 636 arcs of the capture units 631 and 634 of each of the Tiantong Temple are greater than those of the brakes. t % & υ·5犄, for example, when designed as the arc type shown in Figure 10, the curvature is 丨, and the negative dielectrophoretic force generated by the material capture segment 633 (636) can be used to capture concentrated particles, as shown in Figure u. Shown (bio-particle yeast (a/wca-like), but after actual testing, its capture efficiency will be worse than that of the aforementioned capture segments 633, 636. In addition, in this embodiment, the micro-dielectrophoretic wafer The flow channel 5Q has only one shunt segment 502, 503, and the electrode layers 6 are also provided with only two left and right spaced sorting electrodes 61, 62, but in practice, the shunt channels 5〇2, 5〇3 The number may be increased according to the number of particle types to be sorted, and the number of sorting electrodes 61, 62 protruding into the microchannel 50 and the number of the capturing portions 631, 634 of the trapping electrode 63 may be increased to make a plurality of different dielectrics. The particles of the characteristic are gradually sorted into the predetermined splitting sections 501, 502 during the flow of the dielectrophoretic liquid, and are separately captured and concentrated, but are not limited thereto. In summary, through the sorting electrodes 61, 62 and the structure of the capture electrode 63, so that the dielectrophoresis wafer of the present invention can be quickly The particles having different dielectric properties in the dielectrophoresis liquid are separated and guided to a predetermined area, and are designed by the structures of the capturing portions 631 and 634 of the capturing electrodes 63 by 13 200841011, and the particles which are also selected by the knife Capture and gather in a fixed area to facilitate the detection of 疋 / /, 疋 。. When the dielectrophoretic wafer is applied to the detection of biological particles in food or medical U, the various micro-organisms (4) in the sample can be quickly separated and Capturing the agglomeration, thereby saving a lot of time for microbial culture, purification of the strain and the time taken by the Dingli, so that the food inspector or the medical staff can quickly perform microbial characterization and quantification. The purpose of the present invention can be achieved by &
准以上所述者，僅為本發明之一較佳實施例而已，當 不能以此限定本發明實施之範圍，即大凡依本發明申^ 利範圍及發明說明内容所作之簡單的等效變化與修飾$皆 仍屬本發明專利涵蓋之範圍内。 【圖式簡單說明】 圖1是本發明具捕捉濃縮功能之介電泳晶片之_較佳者 施例的立體分解示意圖； 土貝 圖2是該車乂佳貫施例之組合俯視圖，其中一上美板已 微 圖3是該較佳實施例之第—分選電極實際進行 粒之分選時的顯微影像圖； 進行生物微 圖4是該較佳實施例之第二分選電極實際 粒之分選時的顯微影像圖； 圖5是純佳實施例之捕捉電極的第 捉濃縮生物微粒時的顯微影像圖； 灵除福 圖6是類似圖5之視圖，說 弟一捕捉部實際捕捉生 14 200841011 物微粒時的情形； 圖7是該等捕捉電極捕捉不同濃度之生物微粒時，生 物微粒堆積面積與時間之關係圖； 圖8是該等捕捉電極在不同介電泳液流速下，所捕捉 之生物微粒堆積面積隨時變化的關係曲線； 圖9是以拉曼光譜儀對該等捕捉電極之捕捉部所捕捉 聚集之不同生物微粒進行測試之光譜數據； 圖10是類似圖2之視圖，說明等捕捉電極之另一實施 態樣；及 $ …圖11是圖1G之該等捕捉電極實際捕捉生物微粒時的顯The above is only a preferred embodiment of the present invention, and is not intended to limit the scope of the present invention, that is, the simple equivalent changes made by the scope of the invention and the description of the invention. Modifications are still within the scope of the invention. BRIEF DESCRIPTION OF THE DRAWINGS FIG. 1 is a perspective exploded view of a preferred embodiment of a dielectrophoretic wafer having a concentrating function of the present invention; FIG. 2 is a combined top view of the rutting example, one of which is The microplate 3 is a microscopic image of the first sorting electrode of the preferred embodiment when the sorting electrode is actually subjected to particle sorting; and the biological micrograph 4 is the second sorting electrode of the preferred embodiment. FIG. 5 is a microscopic image of the capture electrode of the capture electrode of the purely preferred embodiment; FIG. 5 is a view similar to FIG. Figure 7 is a graph showing the relationship between the bioparticle accumulation area and time when the capture electrodes capture different concentrations of biological particles; Figure 8 is the capture electrode at different dielectrophoresis flow rates. The captured bio-particle accumulation area changes with time; FIG. 9 is the spectral data of the different biological particles captured by the capture portion of the capture electrode by Raman spectroscopy; FIG. 10 is similar to FIG. 11 and FIG significant $ ... 1G is a diagram of the capture of such electrode actually captured when biological particles; view illustrating other embodiment of the electrode to capture a further aspect of
15 200841011 【主要元件符號說明】 3 ....... …上基板 61...... ...第一分選電極 301 .... ...注液孔 611 .... …第一分選部 302··.· …第一排液孔 62…... ...第二分選電極 303 .... …第二排液孔 621 .... ...第二分選部 4....... ....下基板 63...... ...捕捉電極 5 ....... ....流道成型板 631 .... …第一捕捉部 5 0…·. ....微流道 632··.· ...導引段 51..... ....主流段 633 .... ...捕捉段 52•.… ....第一分流段 634.... ，…第二捕捉部 53"·.· ....第二分流段 635 .… .…導引段 6 ...... ....電極層 636… ....捕捉段 1615 200841011 [Description of main component symbols] 3 ....... ...upper substrate 61 ... ... first sorting electrode 301 .... ... liquid injection hole 611 .... ...the first sorting section 302····...the first drain hole 62...the second sorting electrode 303 ....the second drain hole 621 .... ... Second sorting section 4........lower substrate 63.........capturing electrode 5.......................................................................................... ...the first capturing part 5 0...·.....micro-flow channel 632···· ...the guiding section 51........mainstream section 633 .... ...capture Segment 52•...... First diversion section 634....,...Second capture section 53"·......Second diversion section 635 ........Guide section 6 .... .. .... electrode layer 636.... capture segment 16