臺灣博碩士論文加值系統

本論文係配合科技部之「快速定量檢測尿液中CEA/PSA/ALKP 多重腫瘤標幟
非侵入式感測系統」計劃，進行兩項研究主題，分別為可應用於阻抗式生醫感測
器之阻抗估算讀取電路，以及可即時計算阻抗式生醫感測器阻抗值與相位之基頻
電路，皆使用TSMC 0.18 m CMOS Mixed Signal/RF 製程，以驗證設計原理。
本論文之可應用於阻抗式生醫感測器之阻抗估算讀取電路，係利用運算放大
器之反相放大功能，並搭配單元增益緩衝器(unit gain buffer) 建構而成。由於阻抗
式生醫感測器之讀取頻率範圍落在100 Hz 1 MHz，為了增加在讀取時之容錯能
力，因此特意將此電路之操作頻率範圍設計在10 Hz 2 MHz。然而在模擬時並
無BIA-type 生醫感測器之元件可以使用，因此為了確保模擬環境之完整性，利用
電容與電阻建構一個等效模型(RC Model)，而等效模型之阻抗值與相位其變化
趨勢皆與阻抗式生醫感測器相同。晶片量測結果為阻抗值最大誤差為7.7 kΩ (at
10 Hz)，而相位最大誤差為12 (at 50 kHz)。
另外，本論文之可即時計算阻抗值與相位之基頻電路，係為了自動進行估算
阻抗式生醫感測器之阻抗值與相位而延伸設計之數位電路。此基頻電路實現阻抗
估算自動化並且額外增加了即時更新功能，其即時更新功能代表當輸入訊號頻率
或振幅做改變時，其輸出結果也會隨之改變。採用數位訊號計算之原因為其具有
較好的抗雜訊功能，並且與外部溝通較容易等優點。

This thesis was driven by an MOST project, ”Rapid Quantitative Measurement System
for CEA/PSA/ALKP Tumor Markers in Urine,” to develop two research topics, including
an impedance estimation read-out circuit for BIA-type biomedical sensors and an
impedance and phase calculation baseband circuit. Both designs are realized using TSMC
0.18 m CMOS Mixed Signal/RF Process to justify the proposed theory and method.
The first design is an impedance estimation front-end read-out circuit for BIA-type
biomedical sensors, which is composed of low-frequency operational amplifiers and a
unity gain buffer owing to the signal frequency range of the BIA-type biomedical sensors
is 100 Hz 1 MHz. To increase the design margin, the operating frequency range of
the proposed circuit is deliberately selected to be 10 Hz 2 MHz. However, since it is
impossible to include real of BIA-type biomedical sensors in the simulation, an equivalent
model (RC Model) is constructed by capacitors and resistors to ensure the integrity of the
simulated environment. The equivalent model has impedance and phase behavior very
close to that of the BIA-type biosensors. The measurement results on silicon to show
maximum error of 7.7 kΩ at 10 Hz, and the phase maximum error of 12 at 50 kHz.
The baseband circuit calculating the impedance and phase in real time is proposed
to provide a solution carrying out the estimation of the impedance and phase of the BIAtype
biomedical sensors automatically. The baseband circuit is also added with functions
of the instant update of real-time change of the input signal frequency. The reason is that
the digital solution has a better noise rejection capability and feasibility to be integrated
with other digital signal processing modules.

論文審定書. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . i
論文摘要. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . iii
Abstract . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . iv
目錄. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . v
圖目錄. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . viii
表目錄. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . xii
1 概論. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 1
1.1 前言. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 1
1.2 相關文獻與研究探討. . . . . . . . . . . . . . . . . . . . . . . . . . . 4
1.2.1 阻抗估算讀取技術應用. . . . . . . . . . . . . . . . . . . . . . 4
1.2.2 峰值偵測器. . . . . . . . . . . . . . . . . . . . . . . . . . . . 6
1.2.3 除法器. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 9
1.3 研究動機. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 10
1.3.1 可應用於阻抗式生醫感測器之阻抗估算讀取電路. . . . . . . 10
1.3.2 可即時計算阻抗式生醫感測器阻抗值與相位之基頻電路. . . 10
1.4 論文大綱. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 11
2 可應用於阻抗式生醫感測器之阻抗估算讀取電路. . . . . . . . . . . . . . . 12
2.1 簡介. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 12
2.2 阻抗估算讀取電路架構. . . . . . . . . . . . . . . . . . . . . . . . . . 12
2.2.1 OPA 電路介紹. . . . . . . . . . . . . . . . . . . . . . . . . . . 14
2.2.2 阻抗式生醫感測器之等效電阻電容模型. . . . . . . . . . . . 14
2.3 晶片佈局. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 16
2.4 電路模擬結果與預計規格. . . . . . . . . . . . . . . . . . . . . . . . . 17
2.4.1 阻抗式生醫感測器之等效電阻電容模型模擬結果. . . . . . . 17
2.4.2 OPA 模擬結果. . . . . . . . . . . . . . . . . . . . . . . . . . . 19
2.4.3 阻抗估算前端讀取電路模擬結果. . . . . . . . . . . . . . . . 20
2.4.4 預計規格與模擬模擬結果比較. . . . . . . . . . . . . . . . . . 23
2.5 晶片量測結果. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 24
2.5.1 量測環境. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 24
2.5.2 量測結果與分析. . . . . . . . . . . . . . . . . . . . . . . . . . 25
2.5.3 量測結果與模擬結果比較. . . . . . . . . . . . . . . . . . . . 27
2.6 阻抗式生醫感測器量測結果. . . . . . . . . . . . . . . . . . . . . . . 28
2.7 結果與討論. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 32
3 可即時計算阻抗式生醫感測器阻抗值與相位之基頻電路. . . . . . . . . . . 36
3.1 簡介. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 36
3.2 電路架構. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 36
3.3 各子電路設計與原理. . . . . . . . . . . . . . . . . . . . . . . . . . . 39
3.3.1 串列輸入並行輸出電路(SIPO) . . . . . . . . . . . . . . . . . . 39
3.3.2 多工器(MUX) . . . . . . . . . . . . . . . . . . . . . . . . . . . 39
3.3.3 峰值偵測器(Peak_Detector) . . . . . . . . . . . . . . . . . . . 40
3.3.4 振幅計算電路(Calculation_Amplitude) . . . . . . . . . . . . . 43
3.3.5 阻抗計算電路(Calculation_Impedance) . . . . . . . . . . . . . 44
3.3.6 取樣偵測器(Sample_Detector) . . . . . . . . . . . . . . . . . . 46
3.3.7 相位計算電路(Calculation_Phase) . . . . . . . . . . . . . . . . 50
3.3.8 並行輸入串列輸出電路(PISO) . . . . . . . . . . . . . . . . . . 51
3.4 晶片佈局. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 52
3.5 電路模擬結果與預計規格. . . . . . . . . . . . . . . . . . . . . . . . . 53
3.5.1 不同正弦波振幅之模擬結果. . . . . . . . . . . . . . . . . . . 53
3.5.2 不同取樣數之模擬結果. . . . . . . . . . . . . . . . . . . . . . 54
3.6 結果與討論. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 56
4 結論與未來研究方向. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 58
4.1 研究成果與結論. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 58
4.2 未來研究規劃. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 58
參考文獻. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 62

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