6 research outputs found

    A NOVEL WAVEFORM MIRRORING TECHNIQUE FOR SYSTOLIC BLOOD PRESSURE ESTIMATION FROM ANACROTIC PHOTOPLETHYSMOGRAM

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    Continuous cuffless Blood Pressure (BP) measurement is an important tool to monitor the health of individuals at risk. In this study, a new method is proposed for Systolic BP (SBP) estimation utilizing Photoplethysmograms (PPG). To this end, toe and carotid PPG were recorded from seventeen subjects aged 20-28 years, whereas their SBP were measured using a standard BP cuff monitor for validation purpose. The proposed method is based on a novel mirroring technique, which allows for an accurate estimation of the Pulse Transit Time (PTT) from the PPGโ€™s rising part (anacrotic) waveform using an ARX System Identification approach. Based on the modified Moens-Korteweg equation, SBP was then calculated based on the estimated PTT values obtained from the ARX model. The estimated PTT was found to be highly correlated to the measured SBP (R2 = 0.98). Comparison of calculated SBP to the measured SBP obtained using standard BP cuff monitor results in a mean error of 3.4%. Given that 95% of the estimated SBP values are accurate in the +/- 8 mmHg range, this method seems promising for non-invasive, continuous BP monitorin

    An optimization study of estimating blood pressure models based on pulse arrival time for continuous monitoring

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    Continuous blood pressure (BP) monitoring has a significant meaning for the prevention and early diagnosis of cardiovascular disease. However, under different calibration methods, it is difficult to determine which model is better for estimating BP. This study was firstly designed to reveal a better BP estimation model by evaluating and optimizing different BP models under a justified and uniform criterion, i.e., the advanced point-to-point pairing method (PTP). Here, the physical trial in this study caused the BP increase largely. In addition, the PPG and ECG signals were collected while the cuff bps were measured for each subject. The validation was conducted on four popular vascular elasticity (VE) models (MK-EE, L-MK, MK-BH, and dMK-BH) and one representative elastic tube (ET) model, i.e., M-M. The results revealed that the VE models except for L-MK outperformed the ET model. The linear L-MK as a VE model had the largest estimated error, and the nonlinear M-M model had a weaker correlation between the estimated BP and the cuff BP than MK-EE, MK-BH, and dMK-BH models. Further, in contrast to L-MK, the dMK-BH model had the strongest correlation and the smallest difference between the estimated BP and the cuff BP including systolic blood pressure (SBP) and diastolic blood pressure (DBP) than others. In this study, the simple MK-EE model showed the best similarity to the dMK-BH model. There were no significant changes between MK-EE and dMK-BH models. These findings indicated that the nonlinear MK-EE model with low estimated error and simple mathematical expression was a good choice for application in wearable sensor devices for cuff-less BP monitoring compared to others

    ๋Œ€๊ทœ๋ชจ ์ธ๊ตฌ ๋ชจ๋ธ๊ณผ ๋‹จ์ผ ๊ฐ€์Šด ์ฐฉ์šฉํ˜• ์žฅ์น˜๋ฅผ ํ™œ์šฉํ•œ ๋น„์นจ์Šต์  ์—ฐ์† ๋™๋งฅ ํ˜ˆ์•• ๋ชจ๋‹ˆํ„ฐ๋ง ์‹œ์Šคํ…œ

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    ํ•™์œ„๋…ผ๋ฌธ (๋ฐ•์‚ฌ) -- ์„œ์šธ๋Œ€ํ•™๊ต ๋Œ€ํ•™์› : ๊ณต๊ณผ๋Œ€ํ•™ ํ˜‘๋™๊ณผ์ • ๋ฐ”์ด์˜ค์—”์ง€๋‹ˆ์–ด๋ง์ „๊ณต, 2021. 2. ๊น€ํฌ์ฐฌ.์ตœ๊ทผ ์ˆ˜์‹ญ ๋…„ ๋™์•ˆ ๋น„์นจ์Šต์  ์—ฐ์† ํ˜ˆ์•• ๋ชจ๋‹ˆํ„ฐ๋ง์— ๋Œ€ํ•œ ํ•„์š”์„ฑ์ด ์ ์ฐจ ๋Œ€๋‘๋˜๋ฉด์„œ ๋งฅํŒŒ ์ „๋‹ฌ ์‹œ๊ฐ„, ๋งฅํŒŒ ๋„๋‹ฌ ์‹œ๊ฐ„, ๋˜๋Š” ๊ด‘์šฉ์ ๋งฅํŒŒ์˜ ํŒŒํ˜•์œผ๋กœ๋ถ€ํ„ฐ ์ถ”์ถœ๋œ ๋‹ค์–‘ํ•œ ํŠน์ง•๋“ค์„ ์ด์šฉํ•œ ํ˜ˆ์•• ์ถ”์ • ์—ฐ๊ตฌ๋“ค์ด ์ „์„ธ๊ณ„์ ์œผ๋กœ ํ™œ๋ฐœํ•˜๊ฒŒ ์ง„ํ–‰๋˜์—ˆ๋‹ค. ํ•˜์ง€๋งŒ ๋Œ€๋ถ€๋ถ„์˜ ์—ฐ๊ตฌ๋“ค์€ ๊ตญ์ œ ํ˜ˆ์•• ํ‘œ์ค€์„ ๋งŒ์กฑ์‹œํ‚ค์ง€ ๋ชปํ•˜๋Š” ๋งค์šฐ ์ ์€ ์ˆ˜์˜ ํ”ผํ—˜์ž๋“ค ๋งŒ์„ ๋Œ€์ƒ์œผ๋กœ ์ฃผ๋กœ ํ˜ˆ์•• ์ถ”์ • ๋ชจ๋ธ์„ ๊ฐœ๋ฐœ ๋ฐ ๊ฒ€์ฆํ•˜์˜€๊ธฐ ๋•Œ๋ฌธ์— ์„ฑ๋Šฅ์˜ ์ •ํ™•๋„๊ฐ€ ์ ์ ˆํ•˜๊ฒŒ ๊ฒ€์ฆ๋˜์ง€ ๋ชปํ–ˆ๋‹ค๋Š” ํ•œ๊ณ„์ ์ด ์žˆ์—ˆ๊ณ , ๋˜ํ•œ ํ˜ˆ์•• ์ถ”์ • ํŒŒ๋ผ๋ฏธํ„ฐ ์ถ”์ถœ์„ ์œ„ํ•œ ์ƒ์ฒด ์‹ ํ˜ธ๋“ค์„ ์ธก์ •ํ•˜๊ธฐ ์œ„ํ•ด ๋Œ€๋ถ€๋ถ„ ๋‘ ๊ฐœ ์ด์ƒ์˜ ๋ชจ๋“ˆ์„ ํ•„์š”๋กœ ํ•˜๋ฉด์„œ ์‹ค์šฉ์„ฑ ์ธก๋ฉด์—์„œ ํ•œ๊ณ„์ ์ด ์žˆ์—ˆ๋‹ค. ์ฒซ ๋ฒˆ์งธ ์—ฐ๊ตฌ๋Š” ๋Œ€๊ทœ๋ชจ ์ƒ์ฒด์‹ ํ˜ธ ๋ฐ์ดํ„ฐ๋ฒ ์ด์Šค๋“ค์„ ๋ถ„์„ํ•จ์œผ๋กœ์จ ์ž„์ƒ์ ์œผ๋กœ ํ—ˆ์šฉ ๊ฐ€๋Šฅํ•œ ์ˆ˜์ค€์˜ ์ •ํ™•๋„๊ฐ€ ์ ์ ˆํžˆ ๊ฒ€์ฆ๋œ ํ˜ˆ์•• ์ถ”์ • ๋ชจ๋ธ์„ ๊ฐœ๋ฐœํ•˜๋Š” ๊ฒƒ์„ ๋ชฉ์ ์œผ๋กœ ์ง„ํ–‰๋˜์—ˆ๋‹ค. ๋ณธ ์—ฐ๊ตฌ์—์„œ๋Š” 1376๋ช…์˜ ์ˆ˜์ˆ  ์ค‘ ํ™˜์ž๋“ค์˜ ์•ฝ 250๋งŒ ์‹ฌ๋ฐ• ์ฃผ๊ธฐ์— ๋Œ€ํ•ด ์ธก์ •๋œ ๋‘ ๊ฐ€์ง€ ๋น„์นจ์Šต์  ์ƒ์ฒด์‹ ํ˜ธ์ธ ์‹ฌ์ „๋„์™€ ๊ด‘์šฉ์ ๋งฅํŒŒ๋ฅผ ํ™œ์šฉํ•œ ํ˜ˆ์•• ์ถ”์ • ๋ฐฉ์‹๋“ค์„ ๋ถ„์„ํ•˜์˜€๋‹ค. ๋งฅํŒŒ ๋„๋‹ฌ ์‹œ๊ฐ„, ์‹ฌ๋ฐ•์ˆ˜, ๊ทธ๋ฆฌ๊ณ  ๋‹ค์–‘ํ•œ ๊ด‘์šฉ์ ๋งฅํŒŒ ํŒŒํ˜• ํ”ผ์ฒ˜๋“ค์„ ํฌํ•จํ•˜๋Š” ์ด 42 ์ข…๋ฅ˜์˜ ํŒŒ๋ผ๋ฏธํ„ฐ๋“ค์„ ๋Œ€์ƒ์œผ๋กœ ํ”ผ์ฒ˜ ์„ ํƒ ๊ธฐ๋ฒ•๋“ค์„ ์ ์šฉํ•œ ๊ฒฐ๊ณผ, 28๊ฐœ์˜ ํ”ผ์ฒ˜๋“ค์ด ํ˜ˆ์•• ์ถ”์ • ํŒŒ๋ผ๋ฏธํ„ฐ๋กœ ๊ฒฐ์ •๋˜์—ˆ๊ณ , ํŠนํžˆ ๋‘ ๊ฐ€์ง€ ๊ด‘์šฉ์ ๋งฅํŒŒ ํ”ผ์ฒ˜๋“ค์ด ๊ธฐ์กด์— ํ˜ˆ์•• ์ถ”์ • ํŒŒ๋ผ๋ฏธํ„ฐ๋กœ ๊ฐ€์žฅ ์ฃผ์š”ํ•˜๊ฒŒ ํ™œ์šฉ๋˜์—ˆ๋˜ ๋งฅํŒŒ ๋„๋‹ฌ ์‹œ๊ฐ„๋ณด๋‹ค ์šฐ์›”ํ•œ ํŒŒ๋ผ๋ฏธํ„ฐ๋“ค๋กœ ๋ถ„์„๋˜์—ˆ๋‹ค. ์„ ์ •๋œ ํŒŒ๋ผ๋ฏธํ„ฐ๋“ค์„ ํ™œ์šฉํ•˜์—ฌ ํ˜ˆ์••์˜ ๋‚ฎ์€ ์ฃผํŒŒ์ˆ˜ ์„ฑ๋ถ„์„ ์ธ๊ณต์‹ ๊ฒฝ๋ง์œผ๋กœ ๋ชจ๋ธ๋งํ•˜๊ณ , ๋†’์€ ์ฃผํŒŒ์ˆ˜ ์„ฑ๋ถ„์„ ์ˆœํ™˜์‹ ๊ฒฝ๋ง์œผ๋กœ ๋ชจ๋ธ๋ง ํ•œ ๊ฒฐ๊ณผ, ์ˆ˜์ถ•๊ธฐ ํ˜ˆ์•• ์—๋Ÿฌ์œจ 0.05 ยฑ 6.92 mmHg์™€ ์ด์™„๊ธฐ ํ˜ˆ์•• ์—๋Ÿฌ์œจ -0.05 ยฑ 3.99 mmHg ์ •๋„์˜ ๋†’์€ ์ •ํ™•๋„๋ฅผ ๋‹ฌ์„ฑํ•˜์˜€๋‹ค. ๋˜ ๋‹ค๋ฅธ ์ƒ์ฒด์‹ ํ˜ธ ๋ฐ์ดํ„ฐ๋ฒ ์ด์Šค์—์„œ ์ถ”์ถœํ•œ 334๋ช…์˜ ์ค‘ํ™˜์ž๋“ค์„ ๋Œ€์ƒ์œผ๋กœ ๋ชจ๋ธ์„ ์™ธ๋ถ€ ๊ฒ€์ฆํ–ˆ์„ ๋•Œ ์œ ์‚ฌํ•œ ๊ฒฐ๊ณผ๋ฅผ ํš๋“ํ•˜๋ฉด์„œ ์„ธ ๊ฐ€์ง€ ๋Œ€ํ‘œ์  ํ˜ˆ์•• ์ธก์ • ์žฅ๋น„ ๊ธฐ์ค€๋“ค์„ ๋ชจ๋‘ ๋งŒ์กฑ์‹œ์ผฐ๋‹ค. ํ•ด๋‹น ๊ฒฐ๊ณผ๋ฅผ ํ†ตํ•ด ์ œ์•ˆ๋œ ํ˜ˆ์•• ์ถ”์ • ๋ชจ๋ธ์ด 1000๋ช… ์ด์ƒ์˜ ๋‹ค์–‘ํ•œ ํ”ผํ—˜์ž๋“ค์„ ๋Œ€์ƒ์œผ๋กœ ์ ์šฉ ๊ฐ€๋Šฅํ•จ์„ ํ™•์ธํ•˜์˜€๋‹ค. ๋‘ ๋ฒˆ์งธ ์—ฐ๊ตฌ๋Š” ์ผ์ƒ ์ƒํ™œ ์ค‘ ์žฅ๊ธฐ๊ฐ„ ๋ชจ๋‹ˆํ„ฐ๋ง์ด ๊ฐ€๋Šฅํ•œ ๋‹จ์ผ ์ฐฉ์šฉํ˜• ํ˜ˆ์•• ๋ชจ๋‹ˆํ„ฐ๋ง ์‹œ์Šคํ…œ์„ ๊ฐœ๋ฐœํ•˜๋Š” ๊ฒƒ์„ ๋ชฉ์ ์œผ๋กœ ์ง„ํ–‰๋˜์—ˆ๋‹ค. ๋Œ€๋ถ€๋ถ„์˜ ๊ธฐ์กด ํ˜ˆ์•• ์ถ”์ • ์—ฐ๊ตฌ๋“ค์€ ํ˜ˆ์•• ์ถ”์ • ํŒŒ๋ผ๋ฏธํ„ฐ ์ถ”์ถœ์„ ์œ„ํ•ด ํ•„์š”ํ•œ ์ƒ์ฒด์‹ ํ˜ธ๋“ค์„ ์ธก์ •ํ•˜๊ธฐ ์œ„ํ•ด ๋‘ ๊ตฐ๋ฐ ์ด์ƒ์˜ ์‹ ์ฒด ์ง€์ ์— ๋‘ ๊ฐœ ์ด์ƒ์˜ ๋ชจ๋“ˆ์„ ๋ถ€์ฐฉํ•˜๋Š” ๋“ฑ ์‹ค์šฉ์„ฑ ์ธก๋ฉด์—์„œ ํ•œ๊ณ„๋ฅผ ๋‚˜ํƒ€๋ƒˆ๋‹ค. ์ด๋ฅผ ํ•ด๊ฒฐํ•˜๊ธฐ ์œ„ํ•ด ๋ณธ ์—ฐ๊ตฌ์—์„œ๋Š” ์‹ฌ์ „๋„์™€ ๊ด‘์šฉ์ ๋งฅํŒŒ๋ฅผ ๋™์‹œ์— ์—ฐ์†์ ์œผ๋กœ ์ธก์ •ํ•˜๋Š” ๋‹จ์ผ ๊ฐ€์Šด ์ฐฉ์šฉํ˜• ๋””๋ฐ”์ด์Šค๋ฅผ ๊ฐœ๋ฐœํ•˜์˜€๊ณ , ๊ฐœ๋ฐœ๋œ ๋””๋ฐ”์ด์Šค๋ฅผ ๋Œ€์ƒ์œผ๋กœ ์ด 25๋ช…์˜ ๊ฑด๊ฐ•ํ•œ ํ”ผํ—˜์ž๋“ค๋กœ๋ถ€ํ„ฐ ๋ฐ์ดํ„ฐ๋ฅผ ํš๋“ํ•˜์˜€๋‹ค. ์†๊ฐ€๋ฝ์—์„œ ์ธก์ •๋œ ๊ด‘์šฉ์ ๋งฅํŒŒ์™€ ๊ฐ€์Šด์—์„œ ์ธก์ •๋œ ๊ด‘์šฉ์ ๋งฅํŒŒ ๊ฐ„ ํŒŒํ˜•์˜ ํŠน์„ฑ์— ์œ ์˜๋ฏธํ•œ ์ฐจ์ด๊ฐ€ ์žˆ๊ธฐ ๋•Œ๋ฌธ์— ๊ฐ€์Šด์—์„œ ์ธก์ •๋œ ๊ด‘์šฉ์ ๋งฅํŒŒ์—์„œ ์ถ”์ถœ๋œ ํ”ผ์ฒ˜๋“ค์„ ๋Œ€์‘๋˜๋Š” ์†๊ฐ€๋ฝ์—์„œ ์ธก์ •๋œ ๊ด‘์šฉ์ ๋งฅํŒŒ ํ”ผ์ฒ˜๋“ค๋กœ ํŠน์„ฑ์„ ๋ณ€ํ™˜ํ•˜๋Š” ์ „๋‹ฌ ํ•จ์ˆ˜ ๋ชจ๋ธ์„ ๊ฐœ๋ฐœํ•˜์˜€๋‹ค. 25๋ช…์œผ๋กœ๋ถ€ํ„ฐ ํš๋“ํ•œ ๋ฐ์ดํ„ฐ์— ์ „๋‹ฌ ํ•จ์ˆ˜ ๋ชจ๋ธ์„ ์ ์šฉ์‹œํ‚จ ํ›„ ํ˜ˆ์•• ์ถ”์ • ๋ชจ๋ธ์„ ๊ฒ€์ฆํ•œ ๊ฒฐ๊ณผ, ์ˆ˜์ถ•๊ธฐ ํ˜ˆ์•• ์—๋Ÿฌ์œจ 0.54 ยฑ 7.47 mmHg์™€ ์ด์™„๊ธฐ ํ˜ˆ์•• ์—๋Ÿฌ์œจ 0.29 ยฑ 4.33 mmHg๋กœ ๋‚˜ํƒ€๋‚˜๋ฉด์„œ ์„ธ ๊ฐ€์ง€ ํ˜ˆ์•• ์ธก์ • ์žฅ๋น„ ๊ธฐ์ค€๋“ค์„ ๋ชจ๋‘ ๋งŒ์กฑ์‹œ์ผฐ๋‹ค. ๊ฒฐ๋ก ์ ์œผ๋กœ ๋ณธ ์—ฐ๊ตฌ์—์„œ๋Š” ์ž„์ƒ์ ์œผ๋กœ ํ—ˆ์šฉ ๊ฐ€๋Šฅํ•œ ์ˆ˜์ค€์˜ ์ •ํ™•๋„๋กœ ์žฅ๊ธฐ๊ฐ„ ์ผ์ƒ ์ƒํ™œ์ด ๊ฐ€๋Šฅํ•œ ๋น„์นจ์Šต์  ์—ฐ์† ๋™๋งฅ ํ˜ˆ์•• ๋ชจ๋‹ˆํ„ฐ๋ง ์‹œ์Šคํ…œ์„ ๊ฐœ๋ฐœํ•˜๊ณ  ๋‹ค์ˆ˜์˜ ๋ฐ์ดํ„ฐ์…‹์„ ๋Œ€์ƒ์œผ๋กœ ๊ฒ€์ฆํ•จ์œผ๋กœ์จ ๊ณ ํ˜ˆ์•• ์กฐ๊ธฐ ์ง„๋‹จ ๋ฐ ์˜ˆ๋ฐฉ์„ ์œ„ํ•œ ๋ชจ๋ฐ”์ผ ํ—ฌ์Šค์ผ€์–ด ์„œ๋น„์Šค์˜ ๊ฐ€๋Šฅ์„ฑ์„ ํ™•์ธํ•˜์˜€๋‹ค.As non-invasive continuous blood pressure monitoring (NCBPM) has gained wide attraction in the recent decades, many studies on blood pressure (BP) estimation using pulse transit time (PTT), pulse arrival time (PAT), and characteristics extracted from the morphology of photoplethysmogram (PPG) waveform as indicators of BP have been conducted. However, most of the studies have used small homogeneous subject pools to generate models of BP, which led to inconsistent results in terms of accuracy. Furthermore, the previously proposed modalities to measure BP indicators are questionable in terms of practicality, and lack the potential for being utilized in daily life. The first goal of this thesis is to develop a BP estimation model with clinically valid accuracy using a large pool of heterogeneous subjects undergoing various surgeries. This study presents analyses of BP estimation methods using 2.4 million cardiac cycles of two commonly used non-invasive biosignals, electrocardiogram (ECG) and PPG, from 1376 surgical patients. Feature selection methods were used to determine the best subset of predictors from a total of 42 including PAT, heart rate, and various PPG morphology features. BP estimation models were constructed using linear regression, random forest, artificial neural network (ANN), and recurrent neural network (RNN), and the performances were evaluated. 28 features out of 42 were determined as suitable for BP estimation, in particular two PPG morphology features outperformed PAT, which has been conventionally seen as the best non-invasive indicator of BP. By modelling the low frequency component of BP using ANN and the high frequency component using RNN with the selected predictors, mean errors of 0.05 ยฑ 6.92 mmHg for systolic blood pressure (SBP), and -0.05 ยฑ 3.99 mmHg for diastolic blood pressure (DBP) were achieved. External validation of the model using another biosignal database consisting of 334 intensive care unit patients led to similar results, satisfying three international standards concerning the accuracy of BP monitors. The results indicate that the proposed method can be applied to large number of subjects and various subject phenotypes. The second goal of this thesis is to develop a wearable BP monitoring system, which facilitates NCBPM in daily life. Most previous studies used two or more modules with bulky electrodes to measure biosignals such as ECG and PPG for extracting BP indicators. In this study, a single wireless chest-worn device measuring ECG and PPG simultaneously was developed. Biosignal data from 25 healthy subjects measured by the developed device were acquired, and the BP estimation model developed above was tested on this data after applying a transfer function mapping the chest PPG morphology features to the corresponding finger PPG morphology features. The model yielded mean errors of 0.54 ยฑ 7.47 mmHg for SBP, and 0.29 ยฑ 4.33 mmHg for DBP, again satisfying the three standards for the accuracy of BP monitors. The results indicate that the proposed system can be a stepping stone to the realization of mobile NCBPM in daily life. In conclusion, the clinical validity of the proposed system was checked in three different datasets, and it is a practical solution to NCBPM due to its non-occlusive form as a single wearable device.Abstract i Contents iv List of Tables vii List of Figures viii Chapter 1 General Introduction 1 1.1 Need for Non-invasive Continuous Blood Pressure Monitoring (NCBPM) 2 1.2 Previous Studies for NCBPM 5 1.3 Issues with Previous Studies 9 1.4 Thesis Objectives 12 Chapter 2 Non-invasive Continuous Arterial Blood Pressure Estimation Model in Large Population 14 2.1 Introduction 15 2.1.1 Electrocardiogram (ECG) and Photoplethysmogram (PPG) Features for Blood Pressure (BP) Estimation 15 2.1.2 Description of Surgical Biosignal Databases 16 2.2 Feature Analysis 19 2.2.1 Data Acquisition and Data Pre-processing 19 2.2.2 Feature Extraction 25 2.2.3 Feature Selection 35 2.3 Construction of the BP Estimation Models 44 2.3.1 Frequency Component Separation 44 2.3.2 Modelling Algorithms 47 2.3.3 Summary of Training and Validation 52 2.4 Results and Discussion 54 2.4.1 Feature Analysis 54 2.4.1.1 Pulse Arrival Time versus Pulse Transit Time 54 2.4.1.2 Feature Selection 57 2.4.2 Optimization of the BP Estimation Models 63 2.4.2.1 Frequency Component Separation 63 2.4.2.2 Modelling Algorithms 66 2.4.2.3 Comparison against Different Modelling Settings 68 2.4.3 Performance of the Best-case BP Estimation Model 69 2.4.4 Limitations 75 2.5 Conclusion 78 Chapter 3 Development of the Single Chest-worn Device for Non-invasive Continuous Arterial Blood Pressure Monitoring 80 3.1 Introduction 81 3.2 Development of the Single Chest-worn Device 84 3.2.1 Hardware Development 84 3.2.2 Software Development 90 3.2.3 Clinical Trial 92 3.3 Development of the Transfer Function 95 3.3.1 Finger PPG versus Chest PPG 95 3.3.2 The Concept of the Transfer Function 97 3.3.3 Data Acquisition for Modelling of the Transfer Function 98 3.4 Results and Discussion 100 3.4.1 Construction of the Transfer Function 100 3.4.2 Test of the BP Estimation Model 101 3.4.3 Comparison with the Previous Study using the Single Chest-worn Device 104 3.4.4 Limitations 106 3.5 Conclusion 108 Chapter 4 Thesis Summary and Future Direction 109 4.1 Summary and Contributions 110 4.2 Future Work 113 Bibliography 115 Abstract in Korean 129 Acknowledgement 132Docto
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