Law Wing Cheung. / Thesis (M.Phil.)--Chinese University of Hong Kong, 2005. / Includes bibliographical references. / Abstracts in English and Chinese. / Abstract --- p.I / Acknowledgements --- p.V / List of Publications related to this project --- p.VI / Contents --- p.VII / Chapter Chapter 1 --- Introduction --- p.1-1 / Chapter Chapter 2 --- Literature Review / Chapter 2.1 --- Surface Plasmon Waves --- p.2-2 / Chapter 2.2 --- Excitation of Surface Plasmon --- p.2-4 / Chapter 2.2.1 --- Surface Plasmon Coupling Schemes --- p.2-6 / Chapter 2.3 --- Detection Techniques used in SPR sensors --- p.2-13 / Chapter 2.3.1 --- Angular Interrogation --- p.2-14 / Chapter 2.3.2 --- Wavelength Interrogation --- p.2-15 / Chapter 2.3.3 --- Intensity Interrogation --- p.2-16 / Chapter 2.3.4 --- Phase Interrogation --- p.2-16 / Chapter 2.3.5 --- Commercial SPR biosensors --- p.2-18 / Chapter 2.3.6 --- Comparison between Detection Techniques --- p.2-19 / Chapter 2.4 --- Applications of SPR biosensors --- p.2-21 / Chapter Chapter 3 --- Principle of Surface Plasmon Resonance Sensing Technology / Chapter 3.1 --- SPR Phenomenon --- p.3-1 / Chapter 3.2 --- Conditions for Surface Plasmon Resonance --- p.3-5 / Chapter 3.3 --- Wave-vectors --- p.3-7 / Chapter 3.4 --- Surface Plasmon Resonance described by Fresnel's Theory --- p.3-8 / Chapter 3.5 --- Concept of Surface Plasmon Resonance Biosensing --- p.3-10 / Chapter Chapter 4 --- Experiments / Chapter 4.1 --- Highly sensitive differential phase-sensitive surface plasmon resonance biosensor based on Mach-Zehnder configuration --- p.4-1 / Chapter 4.1.1 --- Materials required --- p.4-1 / Chapter 4.1.2 --- Experimental Setup --- p.4-2 / Chapter 4.1.3 --- Principle of Differential Phase Measurement --- p.4-3 / Chapter 4.1.4 --- Photodetector Circuitry --- p.4-6 / Chapter 4.1.5 --- Digital Signal Processing --- p.4-7 / Chapter 4.1.6 --- Polymer based Micro-fluidic System Integrated with SPR Biosensor --- p.4-9 / Chapter 4.2 --- Phase-sensitive Surface Plasmon Resonance Biosensor using the Photoelastic Modulation Technique --- p.4-12 / Chapter 4.2.1 --- Materials required --- p.4-12 / Chapter 4.2.2 --- Experimental Setup --- p.4-13 / Chapter 4.2.3 --- Principle of Photoelastic Modulation Technique and Signal Processing --- p.4-14 / Chapter 4.2.4 --- Operation Principle of Photoelastic Modulator --- p.4-17 / Chapter 4.3 --- Sample Preparations --- p.4-18 / Chapter 4.3.1 --- Glycerin-water Mixtures --- p.4-18 / Chapter 4.3.2 --- "PBS, BSA and BSA antibody" --- p.4-19 / Chapter 4.3.3 --- "RPMI, Trypsin, Cells and SDS" --- p.4-20 / Chapter Chapter5 --- Results amd Discussions / Chapter 5.1 --- Experimental setup I: Highly sensitive differential phase-sensitive surface plasmon resonance biosensor based on Mach-Zehnder configuration --- p.5-1 / Chapter 5.1.1 --- Measuring various glycerin-water concentration mixture with silver-gold sensing layer --- p.5-1 / Chapter 5.1.2 --- Comparison between the sensitivity of our setup and reported setup based on phase detection --- p.5-4 / Chapter 5.1.3 --- Discussion on 0.01° system resolution --- p.5-7 / Chapter 5.1.4 --- Experiment on monitoring BSA-BSA antibody binding reaction --- p.5-9 / Chapter 5.1.5 --- Matching oil and glass slide --- p.5-11 / Chapter 5.1.6 --- Experiments on monitoring BSA-BSA antibody binding reaction with integrated microfluidic system --- p.5-12 / Chapter 5.1.7 --- Experiment on observing cell adhesion properties on gold surface under the influence of trypsin --- p.5-14 / Chapter 5.1.8 --- Discussion on the non-specific binding between trypsin and gold surface --- p.5-16 / Chapter 5.1.9 --- Modifying the gold surface with BSA layer --- p.5-17 / Chapter 5.1.10 --- Experiment on observing cell adhesion properties on the gold surface under the influence Sodium Dodecyl Sulfate (SDS) --- p.5-18 / Chapter 5.2 --- Experimental setup II: Phase-sensitive surface plasmon resonance biosensor using the photoelastic modulation technique --- p.5-21 / Chapter 5.2.1 --- Measurement on difference glycerin-water concentration mixture --- p.5-21 / Chapter 5.2.2 --- Experiment on monitoring BSA-BSA antibody binding reaction --- p.5-23 / Chapter Chapter 6 --- Conclusions and Future Works / Chapter 6.1 --- Conclusions --- p.6-1 / Chapter 6.2 --- Future Works --- p.6-2 / References --- p.R-1 / Appendix / Chapter A. --- Phase Extraction Routine written by Matlab --- p.A-1 / Chapter B. --- Mathematical expressions for calculating the phase angle in the experiment of SPR biosensor using the Photoelastic Modulation Technique --- p.A-6 / Chapter C. --- Relationship between Concentration and Refractive Index of Glycerin-Water Mixture --- p.A-11 / Chapter D. --- Physical Properties of Bovine Serum Albumin --- p.A-12 / Chapter E. --- Simulation Curve written by Matlab --- p.A-13

Detection of oligonucleotide target has been performed with a sandwich assay scheme. We compare the detection performance of strategies using probe oligonucleotide with or without gold nanoparticles (Au-NPs, 20nm) capped on 3'. Our experimental results reveal that while the DNA detection implemented with NIS can provide high sensitivity, both dynamic range and detection limit can be amplified with the aid of Au-NPs on 3' of the probes. The current detection limits of NIS with and without Au-NPs are 0.4 femtomole and 1 nanomole respectively. (Abstract shortened by UMI.) / Finally, this work presents a systematic study of the surface-enhanced Raman-scattering (SERS) properties of nanoparticle island substrates (NIS) and their application for oligonucleotide target detection. To effectively implement SERS on NIS and identify an optimal condition for DNA detection, the relationship between extinction maximum (lambdamax) and SERS enhancement factor (EF) will be explored in detail. This work demonstrates high S/N ratio SERS spectra can be achieved with NIS that has lambdamax located within a spectral window (∼60nm) defined by the excitation wavelength (514nm) and the scattered Raman wavelength. The highest EF measured is about 4x10 8 with a thickness of Ag being 50 A. / In addition, a surface plasmon enhanced ellipsometry (SPEE) biosensor scheme based on the use of a photoelastic modulator (PEM) has been explored. We showed that the polarization parameters of a laser beam, tan psi, cos Delta and ellipse orientation angle &phis;, can be directly measured by detecting the modulation signals at the 1st and 2nd harmonics of the modulation frequency under a certain birefringence geometry. This leads to an accurate measurement of refractive index variations within the evanescent field region close to the gold sensor surface, thereby enabling biosensing applications. Our experimental results confirm that the new scheme offers a decent detection limit of 2x10-7 refractive index unit (RIU) or 5ng/ml of biomolecule solute concentration without any compromise in dynamic range. / We have demonstrated that the sensitivity limit of intensity-based SPR biosensors can be enhanced when we combine the contributions from phase with that of amplitude instead of just detecting the amplitude or phase variation only. Experimental results indicate that an enhancement factor of as much as 20 times is achievable, yet with no compromise in measurement dynamic range. While existing SPR biosensor systems are predominantly based on the angular scheme, which relies on detecting intensity variations associated with amplitude changes only, the proposed scheme may serve as a direct system upgrade approach for these systems. / We have developed a novel design of multi-pass surface plasmon resonance (SPR) biosensor with differential phase interrogation based on multi-pass interferometry. This new configuration provides an intrinsic phase amplification effect of over two-fold by placing the SPR sensor head in a signal arm of the interferometer so that the interrogating optical beam will traverse the sensor surface infinite number of times. Experimental interferometers based on the Michelson and Fabry-Perot configurations have been employed to experimentally verify this amplification effect through the comparison with the Mach-Zehnder configuration. Results obtained from the salt-water mixtures, antibody-antigen, and protein-DNA binding reaction have confirmed the expected phase measurement enhancement. / Yuan, Wu. / Adviser: H. P. Ho. / Source: Dissertation Abstracts International, Volume: 70-06, Section: B, page: 3582. / Thesis (Ph.D.)--Chinese University of Hong Kong, 2008. / Includes bibliographical references (leaves 115-132). / Electronic reproduction. Hong Kong : Chinese University of Hong Kong, [2012] System requirements: Adobe Acrobat Reader. Available via World Wide Web. / Electronic reproduction. [Ann Arbor, MI] : ProQuest Information and Learning, [200-] System requirements: Adobe Acrobat Reader. Available via World Wide Web. / Abstracts in English and Chinese. / School code: 1307.

Oxytocin (OXT), a neuropeptide synthesized in the paraventricular nucleus (PVN) of the hypothalamus, functions to increase the precedence of social stimuli and promote the development of a wide range of social behaviors. However, whether OXT has a predicting role in social reward has yet to be examined. In this study, we developed a genetically encoded, scalable OXT sensor named OXTR-iTango2 and applied this technique to define the role of OXT in learned social behaviors. OXTR-iTango2 enables the combination of light- and ligand- dependent gene expression both in vitro and in vivo neural systems. In order to study the predictive role of OXT during expected socially rewarding experiences, we first conditioned animals to a social environment, and then selectively labeled OXT-sensitive ventral tegmental area dopamine (VTA-DA) neurons when animals encountered a conditioned stimulus that stood to predict a familiar social reward. Recurrent exposure to the same social stimulus normally lowered the degree of social interaction, but this reduced interaction was not observed when OXT-sensitive DA neurons were optogenetically inhibited. Thus, our findings support the notion that OXT plays a role beyond promoting social interactions, leading for a new proposed hypothesis that OXT mediation also leads to active avoidance of mundane social interactions. / Includes bibliography. / Dissertation (Ph.D.)--Florida Atlantic University, 2020. / FAU Electronic Theses and Dissertations Collection

近年來感測器、集成電路及無線通信的科技迅速發展，促使IEEE802.15工作小組6（TG6）致力硏究一個新的無線通信標準─人體區域網路（BAN）。這個新標準特別考量在人體上、人體內或人體周邊的應用。雖然BAN至今還未達成最後定案，不同類型的應用方案已被廣泛提出。這些方案可分為醫療應用（例如：生命徵象感測和植入式治療）及非醫療應用（例如：消費性電子、個人娛樂和遙遠控制）。無線感測節點〈WSN）的基本要求包括輕巧、廉價及低耗電量。因此，本論文提出了一個符合以上要求的注入式鎖態發射機。此外，我們設計了三個發射機的內部模組。由於BAN的物理層例如調變方式和頻譜配置還未完全製訂，本文的電路設計將基於IEEE802.15 TG6的初步建議。 / 第一個模組是一個利用同相位雙路輸入及電流再使用技術的次毫瓦、第一次諧波LC注入式鎖態振盪器〈ILO）。該振盪器操作範圍在醫療植入式通訊服務〈MICS）頻段，並已採用了0.13-μm CMOS工藝實現而僅佔有200 m x 380 m芯片面積。實驗結果表明，在輸入動力0 dBm時，其鎖定範圍可達800 MHz (150 950 MHz) 。最重要的是，該ILO擁有-30 dBm的高輸入靈敏度，同時在1-V供電下只消耗660 A靜態電流。超低的靜態電流使WSN能從人體收集能量而變得完全自主。 / 第二個模組是一個低功耗MICS非整數型頻率合成器，其目的在於選擇信道。雖然整數鎖相環由於其低複雜性而被廣泛使用，對MICS頻段而言並不是一項良好方案。主要原因在於其信道寬只有300 kHz，速度、頻率解析度和相位雜訊變得很難平衡。為此，我們採用0.13-μm CMOS製程設計了一個4階第二型和差積分〈Σ-）調變器分數鎖相環。為了抑制混附單頻信號，二階單迴路數字Σ-調變器加入了抖動。仿真結果顯示該頻率合成器能在15 s內鎖定，同時在1.5-V供電下只消耗4 mW功耗。 / 第三個模組是一個高效能、完全集成的E類功率放大器〈PA）。該PA採用了自給偏壓反相器作為前置放大器，操作範圍在MICS頻段及工業、科學和醫學〈ISM）頻段。在0.18-m CMOS工藝下實現的該PA佔有0.9 mm x 0.7 mm芯片面積。實驗結果表明，在1.2-V供電下及操作頻率是433 MHz時，該PA的漏極效率及輸出功率分別可達40.2 %和14.7 dBm。當操作頻率從380 MHz 到460 MHz，該PA仍能保侍最少34.7 %的漏極效率。此設計適用於低數據傳輸率、固定振幅調變，例如：QPSK、OQPSK等。 / Recent technological advances in sensors, integrated circuits and wireless communication enable miniature devices located on, in or around the human body to form a new wireless communication standard called wireless Body Area Network (BAN). Although BAN is still being investigated by the IEEE 802.15 Task Group 6 (TG6), a vast variety of applications has been proposed which can be categorized into medical applications (e.g. vital signs monitoring and implantable therapeutic treatment) and non-medical applications (e.g. consumer electronics and remote control). The basic requirements of each Wireless Sensor Node (WSN) include light weight, small form-factor, low cost and low power consumption. This thesis proposes an injection-locked transmitter which is a potential candidate to minimize the power consumption of the RF transmitter in WSNs. Three circuit blocks in the proposed injection-locked transmitter are designed and implemented. Since the physical layer of BAN, such as modulation scheme and frequency allocation, has still not been finalized yet, the prototypes in this thesis are designed based on the preliminary suggestions made by the IEEE 802.15 TG6. / The first circuit block is a sub-mW, current-reused first-harmonic LC injection-locked oscillator (ILO) using in-phase dual-input injection technique, operating in the Medical Implantable Communications Service (MICS) band from 402MHz to 405 MHz for medical implants. It has been fabricated in a standard 0.13-m CMOS technology; occupying 200 m x 380 m. Measurement results show that the proposed ILO features a wide locking range of 800 MHz (150-950 MHz) at input power of 0 dBm. More importantly, it has a high input sensitivity of -30 dBm to lock the 3-MHz bandwidth of the MICS band, while consuming only 660 W at 1-V supply. This ultra-low power consumption enables autonomous WSNs by energy harvested from the human body. / The second circuit block is a low power MICS fractional-N frequency synthesizer for channel selection. Although integer-N phase-locked loop (PLL) is widely used due to its low circuit complexity, it is not considered as a good solution for MICS band where the channel spacing is just 300 kHz, due to the severe trade-off between speed, frequency resolution and phase noise performance. To solve this issue, a 4th-order type-II Σ- fractional-N PLL is designed using a standard 0.18-m CMOS technology. A 2nd-order single-loop digital Σ- modulator with dither is designed to eliminate the spurious tones. Simulation results verify that the synthesizer achieves 15 s locking time and consumes 4 mW at a power supply of 1.5 V. / Finally, a power-efficient fully-integrated class-E power amplifier with a self-biased inverter used as a preamplifier stage has been implemented in a standard 0.18-m CMOS process, with 0.9 mm x 0.7 mm active area. It operates in both MICS band for implantable devices and Industrial, Scientific and Medical (ISM) band for wearable devices. Experimental results shows that it achieves 40.2 % drain efficiency while output power is 14.7 dBm at 433 MHz under 1.2-V supply. Moreover, the drain efficiency maintains at least 34.7 % over the frequency range from 380 MHz to 460 MHz. This design is suitable for low data-rate, constant envelope modulation, such as QPSK, OQPSK, etc. / Detailed summary in vernacular field only. / Detailed summary in vernacular field only. / Detailed summary in vernacular field only. / Detailed summary in vernacular field only. / Li, Kwan Wai. / Thesis (Ph.D.)--Chinese University of Hong Kong, 2012. / Includes bibliographical references. / Electronic reproduction. Hong Kong : Chinese University of Hong Kong, [2012] System requirements: Adobe Acrobat Reader. Available via World Wide Web. / Abstract also in Chinese. / Abstract of thesis entitled: --- p.I / 摘要 --- p.IV / Contents --- p.VI / List of Figures --- p.XI / List of Tables --- p.XVII / Acknowledgement --- p.XVIII / Chapter CHAPTER 1. --- Introduction --- p.1 / Chapter 1.1 --- Motivation for body area network (BAN) --- p.1 / Chapter 1.2 --- Standardization of BAN and its positioning between different communication technologies --- p.3 / Chapter 1.3 --- Classification of BAN and its potential applications --- p.5 / Chapter 1.4 --- Requirements and challenges of BAN --- p.7 / Chapter 1.5 --- Research objectives and organization of this dissertation --- p.9 / References --- p.11 / Chapter CHAPTER 2. --- Background information of biomedical transceivers --- p.12 / Chapter 2.1 --- MICS band --- p.12 / Chapter 2.1.1 --- Frequency allocation --- p.12 / Chapter 2.1.2 --- Output power --- p.13 / Chapter 2.1.3 --- Transmit spectral mask --- p.14 / Chapter 2.1.4 --- Transmit center frequency tolerance --- p.14 / Chapter 2.1.5 --- Channel model --- p.15 / Chapter 2.1.6 --- Link budget --- p.17 / Chapter 2.2 --- Fundamental figure of merits for transceivers --- p.18 / Chapter 2.2.1 --- Noise figure, noise floor and receiver sensitivity --- p.18 / Chapter 2.2.2 --- Transmitter energy efficiency --- p.19 / References --- p.20 / Chapter CHAPTER 3. --- Review of transmitter architectures --- p.21 / Chapter 3.1 --- Overview --- p.21 / Chapter 3.2 --- Architectures --- p.22 / Chapter 3.2.1 --- Quadrature --- p.22 / Chapter 3.2.2 --- Polar --- p.23 / Chapter 3.2.3 --- PLL-based --- p.24 / Chapter 3.2.4 --- Injection-locked --- p.26 / Chapter 3.3 --- Radio architecture selection for biomedical systems in BAN --- p.27 / Chapter 3.3.1 --- Data-rate --- p.27 / Chapter 3.3.2 --- Modulation scheme --- p.28 / Chapter 3.3.3 --- Proposed transmitter architecture --- p.28 / References --- p.31 / Chapter CHAPTER 4. --- Design of sub-mW injection-locked oscillator --- p.33 / Chapter 4.1 --- Introduction --- p.34 / Chapter 4.2 --- Circuit design and analysis --- p.34 / Chapter 4.3 --- Experimental results --- p.47 / Chapter 4.4 --- Summary --- p.55 / References --- p.56 / Chapter CHAPTER 5. --- Design of low-power fractional-N frequency synthesizer --- p.58 / Chapter 5.1 --- Synthesizer architectures --- p.59 / Chapter 5.2 --- PLL design fundamentals --- p.63 / Chapter 5.2.1 --- Stability --- p.63 / Chapter 5.2.2 --- Phase noise --- p.65 / Chapter 5.3 --- Proposed architecture --- p.67 / Chapter 5.4 --- System design --- p.68 / Chapter 5.4.1 --- Stability --- p.68 / Chapter 5.4.2 --- Phase noise --- p.73 / Chapter 5.5 --- Σ modulation in fractional-N synthesis --- p.75 / Chapter 5.5.1 --- Basic operating principles --- p.76 / Chapter 5.5.2 --- An accumulator as a first-order Σ- modulator --- p.78 / Chapter 5.5.3 --- Noise analysis --- p.80 / Chapter 5.5.4 --- Architectures --- p.84 / Chapter 5.5.5 --- Design and modeling --- p.87 / Chapter 5.5.6 --- Digital circuit implementation --- p.99 / Chapter 5.5.7 --- Measurement results --- p.104 / Chapter 5.6 --- Time domain behavioral modeling --- p.104 / Chapter 5.7 --- Design of building blocks --- p.106 / Chapter 5.7.1 --- VCO --- p.107 / Chapter 5.7.1.1 --- Principles --- p.107 / Chapter 5.7.1.2 --- Circuit design --- p.111 / Chapter 5.7.2 --- PFD --- p.131 / Chapter 5.7.2.1 --- Principles --- p.131 / Chapter 5.7.2.2 --- Circuit design --- p.133 / Chapter 5.7.3 --- CP --- p.136 / Chapter 5.7.3.1 --- Principles --- p.136 / Chapter 5.7.3.2 --- Circuit design --- p.137 / Chapter 5.7.4 --- Frequency divider --- p.138 / Chapter 5.7.4.1 --- Principles --- p.138 / Chapter 5.7.4.2 --- Circuit design --- p.145 / Chapter 5.7.5 --- Loop filter --- p.148 / Chapter 5.8 --- Layout issues --- p.149 / Chapter 5.9 --- Overall simulation results --- p.150 / Chapter 5.1 --- Summary --- p.152 / References --- p.153 / Chapter CHAPTER 6. --- Design of high-efficient power amplifier --- p.154 / Chapter 6.1 --- Classification of PAs --- p.154 / Chapter 6.2 --- Circuit design considerations --- p.158 / Chapter 6.3 --- Experimental results --- p.160 / Chapter 6.4 --- Summary --- p.164 / References --- p.166 / Chapter CHAPTER 7. --- Conclusions and future work --- p.167 / Chapter 7.1 --- Conclusions --- p.167 / Chapter 7.2 --- Future work --- p.168 / References --- p.171

Ho, Wai-to Antony. / Thesis (M.Phil.)--Chinese University of Hong Kong, 2001. / Includes bibliographical references (leaves 100-102). / Abstracts in English and Chinese. / Abstract --- p.I / Acknowledgement --- p.III / Table of Content --- p.IV / List of Figures --- p.VI / List of Tables --- p.X / List of Charts --- p.XI / Chapter CHAPTER 1: --- INTRODUCTION --- p.1 / Chapter 1.1 --- Biomedical sensing --- p.1 / Chapter 1.2 --- Bone Fracture --- p.2 / Chapter 1.3 --- Bone Fracture Treatment --- p.3 / Chapter 1.4 --- Objectives --- p.4 / Chapter CHAPTER 2: --- LITERATURE SURVEY --- p.5 / Chapter 2.1 --- Bone Structure --- p.5 / Chapter 2.2 --- Biomechanics in Bone Fracture --- p.10 / Chapter 2.3 --- Mathematical Model on Bending and Fracture --- p.11 / Chapter 2.4 --- Intramedullary nailing --- p.12 / Chapter 2.5 --- Reaming technique for intramedullary nailing --- p.14 / Chapter 2.6 --- More on reaming technique --- p.16 / Chapter 2.7 --- Existing pressure-monitoring system of reaming operation --- p.18 / Chapter 2.8 --- Biomedical sensation --- p.19 / Chapter CHAPTER 3: --- SYSTEM DESIGN: RE-ENGINEERING OF A BONE REAMING SYSTEM --- p.23 / Chapter 3.1 --- Mechanical Design-Bone Reaming Guide Rod --- p.23 / Chapter 3.2 --- Guide Rod --- p.24 / Chapter 3.2.1 --- Guide Rod: Head --- p.25 / Chapter 3.2.2 --- Guide Rod: Rod Body --- p.32 / Chapter 3.2.3 --- Guide Rod: Tail --- p.41 / Chapter 3.3 --- Connection System --- p.43 / Chapter 3.3.1 --- Connection System: Components --- p.44 / Chapter 3.3.2 --- Connection System: Connection Mechanism --- p.50 / Chapter 3.3.3 --- Connection System: Disconnection Mechanism --- p.53 / Chapter 3.4 --- Signal Transmission Mechanism --- p.54 / Chapter 3.5 --- Plastic Case --- p.57 / Chapter 3.6 --- Selection of Microsensor --- p.59 / Chapter CHAPTER 4: --- SIGNAL CONDITIONING & PROCESSING --- p.62 / Chapter 4.1 --- Signal Conditioning and Processing --- p.62 / Chapter 4.2 --- Voltage Regulation --- p.62 / Chapter 4.3 --- Instrumentation Amplification --- p.64 / Chapter 4.4 --- Noise Filtering --- p.66 / Chapter 4.5 --- Signal Processing Software --- p.66 / Chapter CHAPTER 5: --- EXPERIMENTAL SETUP --- p.68 / Chapter 5.1 --- Experiments --- p.68 / Chapter 5.2 --- MEMS Pressure Sensor --- p.68 / Chapter 5.3 --- Voltage Regulation Experiment --- p.70 / Chapter 5.4 --- Noise Filtering Experiment --- p.70 / Chapter 5.5 --- Rotating Bearing Signal Transmission System --- p.74 / Chapter 5.6 --- Guide Rod System Calibration Experiment --- p.76 / Chapter 5.6.1 --- Calibration Experiment-Stationary --- p.79 / Chapter 5.6.2 --- Calibration Experiment-Dynamic --- p.79 / Chapter CHAPTER 6: --- EXPERIMENTAL RESULTS --- p.80 / Chapter 6.1 --- Results --- p.80 / Chapter 6.2 --- MEMS Pressure Sensor --- p.80 / Chapter 6.3 --- Voltage Regulation Experiment --- p.81 / Chapter 6.4 --- Noise Filtering Experiment --- p.82 / Chapter 6.5 --- Rotating Bearing Signal Transmission System --- p.83 / Chapter 6.5.1 --- Non-rotating experiment --- p.83 / Chapter 6.5.2 --- Rotating experiment --- p.84 / Chapter 6.5.2.1 --- Rotating experiment -Unprocessed --- p.84 / Chapter 6.5.2.2 --- Rotating experiment -Noise Filtering --- p.86 / Chapter 6.6 --- Guide Rod System Calibration Experiment --- p.89 / Chapter 6.6.1 --- Calibration experiment-Stationary System Calibration --- p.89 / Chapter 6.6.2 --- Rotating experiment-Rotating Speed Calibration --- p.91 / Chapter 6.6.2.1 --- Influence of rotation motion on fluidic pressure --- p.91 / Chapter 6.6.2.2 --- Calibration Experiment --- p.94 / Chapter CHAPTER 7: --- CONCLUSION --- p.98 / Chapter CHAPTER 8: --- REFERENCE --- p.100 / Appendix --- p.103

Diss. (sammanfattning) Stockholm : Karol. inst., 2005. / Härtill 6 uppsatser.

Diss. (sammanfattning) Stockholm : Tekn. högsk. / Härtill 4 uppsatser.

Wu, Kin Fai. / Thesis (M.Phil.)--Chinese University of Hong Kong, 2008. / Includes bibliographical references (leaves 88-91). / Abstracts in English and Chinese. / Abstract --- p.i / 槪要 --- p.ii / Acknowledgements --- p.iii / Table of Contents --- p.iv / List of Figures --- p.vi / List of Tables --- p.x / Chapter Chapter 1 --- Introduction --- p.1 / Chapter 1.1 --- Motivation --- p.1 / Chapter 1.2 --- Outline of the Proposed Design --- p.2 / Chapter 1.3 --- Purposes of the Present Study --- p.2 / Chapter Chapter 2 --- Background and Literature Review --- p.4 / Chapter 2.1 --- Electrocardiogram --- p.4 / Chapter 2.2 --- Conventional ECG Measurement --- p.7 / Chapter 2.3 --- Heart Rate --- p.8 / Chapter 2.4 --- Heart Rate Variability --- p.9 / Chapter 2.5 --- Capacitive Sensing --- p.11 / Chapter 2.6 --- Review of ECG Monitoring System by Capacitive Sensing On a Sleeping Bed --- p.14 / Chapter Chapter 3 --- System Design and Implementation --- p.17 / Chapter 3.1 --- Hardware --- p.17 / Chapter 3.1.1 --- Bedsheet Sensor --- p.17 / Chapter 3.1.2 --- Pre-amplifier --- p.21 / Chapter 3.1.3 --- Measuring Device --- p.30 / Chapter 3.1.4 --- Power Supply & PCB Layout --- p.49 / Chapter 3.2 --- Software --- p.52 / Chapter 3.2.1 --- Detection of R Waves --- p.52 / Chapter 3.2.2 --- Tracking of HR & Mean RR Intervals --- p.55 / Chapter 3.2.3 --- Estimation of Signal-to-Noise Ratios --- p.56 / Chapter Chapter 4 --- Preliminary Tests on the Functionality of the Proposed System --- p.57 / Chapter 4.1 --- Test I - Test on the Arrangement of Electrodes --- p.57 / Chapter 4.1.1 --- Methods --- p.57 / Chapter 4.1.2 --- Results --- p.60 / Chapter 4.2 --- Test II - Test on the ECG Measurement of Subjects in Different Sleeping Postures --- p.64 / Chapter 4.2.1 --- Methods --- p.64 / Chapter 4.2.2 --- Results --- p.65 / Chapter Chapter 5 --- Experiments on the Performance of Continuous Monitoring of ECG and HR --- p.69 / Chapter 5.1 --- Experiment I - Experiment on the Reliability of the Proposed System for Continuous Monitoring of ECG and HR on Thirty Subjects --- p.69 / Chapter 5.1.1 --- Methods --- p.70 / Chapter 5.1.2 --- Results --- p.70 / Chapter 5.2 --- Experiment II - Experiment on the Feasibility of the Proposed System for Continuous Monitoring of ECG and HR on a Subject During an Eight-hour Sleep --- p.75 / Chapter 5.2.1 --- Materials --- p.76 / Chapter 5.2.2 --- Methods --- p.76 / Chapter 5.2.3 --- Results --- p.77 / Chapter Chapter 6 --- Discussions --- p.81 / Chapter 6.1 --- Selection of the Passband of the Proposed Circuit --- p.81 / Chapter 6.2 --- Arrangement of Electrodes on the Bedsheet --- p.82 / Chapter 6.3 --- Practical Design of Electrodes --- p.83 / Chapter 6.4 --- Performance of Continuous Monitoring of HR by Using the Proposed System --- p.84 / Chapter Chapter 7 --- Conclusion --- p.86 / References --- p.88

Chan, Chun Hung. / Thesis (M.Phil.)--Chinese University of Hong Kong, 2008. / Includes bibliographical references (leaves 77-84). / Abstracts in Chinese and English. / Acknowledgment: --- p.i / 摘要 --- p.ii / Abstract --- p.iv / List of Figure --- p.vi / List of Table --- p.viii / Content Page --- p.ix / Chapter Chapter 1 --- Introduction --- p.1 / Chapter 1.1 --- The Difficulties --- p.1 / Chapter 1.2 --- The Solution --- p.2 / Chapter 1.3 --- Goal of the Present Work --- p.2 / Chapter Chapter 2 --- Background and Methodology --- p.3 / Chapter 2.1 --- Hypertension Situation and Problems Around the World --- p.3 / Chapter 2.1.1 --- Blood Pressure Variability (BPV) --- p.4 / Chapter 2.2 --- Blood Pressure Measuring Methods --- p.5 / Chapter 2.2.1 --- Traditional Blood Pressure Meters --- p.6 / Chapter 2.2.2 --- Limitation of Commercial Blood Pressure Meters --- p.7 / Chapter 2.2.3 --- Pulse-Transit-Time (PTT) Based Blood Pressure Measuring Watch --- p.7 / Chapter 2.3 --- Wearable Body Sensors Network / System --- p.8 / Chapter 2.4 --- Current Status of e-Textile Garment --- p.9 / Chapter 2.4.1 --- Blood Pressure Measurement in e-Textile Garment --- p.13 / Chapter 2.5 --- Wearable Intelligent Sensors and System for e-Health (WISSH) --- p.15 / Chapter 2.5.1 --- "Monitoring, Connection and Display" --- p.15 / Chapter 2.5.2 --- Treatment --- p.16 / Chapter 2.5.3 --- Alarming --- p.17 / Chapter Chapter 3 --- "A h-Shirt to Non-invasive, Continuous Monitoring of Arterial Blood Pressure" --- p.18 / Chapter 3.1 --- Design and Inner Structure of h-Shirt --- p.18 / Chapter 3.1.1 --- Choose of e-Textile Material --- p.21 / Chapter 3.1.2 --- Design of ECG Circuit --- p.23 / Chapter 3.1.3 --- Design of PPG Circuit --- p.26 / Chapter 3.2 --- Blood Pressure Estimation Using Pulse-Transit-Time Algorithm --- p.28 / Chapter 3.2.1 --- Principal --- p.28 / Chapter 3.2.2 --- Equations --- p.29 / Chapter 3.2.3 --- Calibration --- p.29 / Chapter 3.3 --- Performance Tests on h-Shirt --- p.30 / Chapter 3.3.1 --- Test I: BP Measurement Accuracy --- p.30 / Chapter 3.3.2 --- Test I: Procedure and Protocol --- p.30 / Chapter 3.3.3 --- Test I-Results --- p.31 / Chapter 3.3.4 --- Test II: Continuality BP Estimation Performance --- p.31 / Chapter 3.3.5 --- Test II - Experiment Procedure and Protocol --- p.32 / Chapter 3.3.6 --- Test II - Experiment Result --- p.33 / Chapter 3.3.7 --- Test II 一 Discussion --- p.43 / Chapter 3.4 --- Follow-up Tests on ECG Circuit --- p.47 / Chapter 3.4.1 --- Problems --- p.47 / Chapter 3.4.2 --- Assumptions --- p.48 / Chapter 3.4.3 --- Experiment Protocol and Setup --- p.48 / Chapter 3.4.4 --- Experiment Results --- p.53 / Chapter 3.4.5 --- Discussion --- p.56 / Chapter Chapter 4: --- Hybrid Body Sensor Network in h-Shirt --- p.59 / Chapter 4.1 --- A Hybrid Body Sensor Network --- p.59 / Chapter 4.2 --- Biological Channel Used in h-Shirt --- p.60 / Chapter 4.3 --- Tests of Bio-channel Performance --- p.62 / Chapter 4.3.1 --- Experiment Protocol --- p.62 / Chapter 4.3.2 --- Results --- p.62 / Chapter 4.4 --- Discussion and Conclusion --- p.63 / Chapter Chapter 5: --- Conclusion and Suggestions for Future Works --- p.66 / Chapter 5.1 --- Conclusion --- p.66 / Chapter 5.1.1 --- Structure of h-Shirt --- p.66 / Chapter 5.1.2 --- Blood Pressure Estimating Ability of h-Shirt --- p.67 / Chapter 5.1.3 --- Tests and Amendments on h-Shirt ECG Circuit --- p.67 / Chapter 5.1.4 --- Hybrid Body Sensor Network in h-Shirt --- p.67 / Chapter 5.2 --- Suggestions for Future Work --- p.68 / Chapter 5.2.1 --- Further Development of Bio-channel Biological Model --- p.68 / Chapter 5.2.2 --- Positioning and Motion Sensing with h-Shirt --- p.69 / Chapter 5.2.3 --- Implementation of Updated Advance Technology into h-Shirt --- p.69 / Appendix: Non-invasive BP Measuring Device - Finometer --- p.71 / Reference: --- p.77

No / Keratinocyte traction forces play a crucial role in wound healing. The aim of this study was to develop a novel cell traction force (CTF) transducer system based on cholesteryl ester liquid crystals (LC). Keratinocytes cultured on LC induced linear and isolated deformation lines in the LC surface. As suggested by the fluorescence staining, the deformation lines appeared to correlate with the forces generated by the contraction of circumferential actin filaments which were transmitted to the LC surface via the focal adhesions. Due to the linear viscoelastic behavior of the LC, Hooke's equation was used to quantify the CTFs by associating Young's modulus of LC to the cell induced stresses and biaxial strain in forming the LC deformation. Young's modulus of the LC was profiled by using spherical indentation and determined at approximately 87.1+/-17.2kPa. A new technique involving cytochalasin-B treatment was used to disrupt the intracellular force generating actin fibers, and consequently the biaxial strain in the LC induced by the cells was determined. Due to the improved sensitivity and spatial resolution ( approximately 1mum) of the LC based CTF transducer, a wide range of CTFs was determined (10-120nN). These were found to be linearly proportional to the length of the deformations. The linear relationship of CTF-deformations was then applied in a bespoke CTF mapping software to estimate CTFs and to map CTF fields. The generated CTF map highlighted distinct distributions and different magnitude of CTFs were revealed for polarized and non-polarized keratinocytes.