A quantitative study for body perspiration with conductivity-based humidity sensing system

Bin Wha Chang, Shoou Jeng Yeh, Ping Ping Tsai, Hsien-Chang Chang

Research output: Contribution to journalArticle

Abstract

The whole measuring system in this study was composed of temperature sensor (a T type of nickel-copper alloy), humidity sensor, flow meter, conductimeter and personal computer. The mini-chip humidity sensor with temperature compensation was fabricated by a conductive poly-(2-acrylamido-2-methyl-propane sulfonate) layer coated on an interdigitated style electrode surface, and was used to detect the slight variation of relative humidity (RH) in a 0.5 ml of closed space. The detection range for RH was 30 to 90 %RH with respect to the conductance response from 1 μS to 85 mS, and the resolution was obtained to be 6 %RH mS-1. This sensor unit was placed on a specific skin surface for sweating monitor and recorded the electrical signal output. Three indexes were characterized for sweating quantification in our experiments. (1) The maximum sweating rate (MSR, %RHmin-1), being used to calculate the first derivative from the sweating data in the first two minute, is acceleration ability for sweat gland to sweating. (2) The partial area of sweating (SPA, %RH min), being used to evaluate the kinetic function of sweating by the SPA obtained from the time with RH value integral in the first two minute. (3) The whole area of sweating (SWA, %RH min), being got from the total area calculation for a complete interval, described the actual amount of sweating in monitor phase. These (MSR, SPA, SWA) values were statistically tried to estimate the sweating difference for any body areas. Based on our results, the average of R and L palms (87.3 ± 4.71, 60.46 ± 2.28, 123.12 ± 10.9, n=12) and the average of R and L soles (78.167 ± 6.128, 42.33 ± 6.6, 133.67 ± 14.61, n=11) were more significant for sweating than chest (44.5 ± 1.87, 23.0 ± 0.89, 99 ± 3.6, n=6) and back (43.7 ± 2.5, 25.16 ± 1.47, 103.5 ± 1.87, n=6). This result was found to be well matching to the actual distribution of sweat gland in body. Therefore, the device with conductivity-based humidity sensing system is practicable in clinical sweat monitoring.

Original languageEnglish
Pages (from-to)197-204
Number of pages8
JournalJournal of Medical and Biological Engineering
Volume21
Issue number4
Publication statusPublished - 2001

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Sweating
Humidity
Atmospheric humidity
Humidity sensors
Sweat Glands
Copper alloys
Nickel alloys
Temperature sensors
Propane
Personal computers
Temperature
Sweat
Skin
Microcomputers
Derivatives
Electrodes
Kinetics
Monitoring
Thorax
Sensors

All Science Journal Classification (ASJC) codes

  • Biophysics

Cite this

@article{942ecd6b105943319917bf5574fe34f4,
title = "A quantitative study for body perspiration with conductivity-based humidity sensing system",
abstract = "The whole measuring system in this study was composed of temperature sensor (a T type of nickel-copper alloy), humidity sensor, flow meter, conductimeter and personal computer. The mini-chip humidity sensor with temperature compensation was fabricated by a conductive poly-(2-acrylamido-2-methyl-propane sulfonate) layer coated on an interdigitated style electrode surface, and was used to detect the slight variation of relative humidity (RH) in a 0.5 ml of closed space. The detection range for RH was 30 to 90 {\%}RH with respect to the conductance response from 1 μS to 85 mS, and the resolution was obtained to be 6 {\%}RH mS-1. This sensor unit was placed on a specific skin surface for sweating monitor and recorded the electrical signal output. Three indexes were characterized for sweating quantification in our experiments. (1) The maximum sweating rate (MSR, {\%}RHmin-1), being used to calculate the first derivative from the sweating data in the first two minute, is acceleration ability for sweat gland to sweating. (2) The partial area of sweating (SPA, {\%}RH min), being used to evaluate the kinetic function of sweating by the SPA obtained from the time with RH value integral in the first two minute. (3) The whole area of sweating (SWA, {\%}RH min), being got from the total area calculation for a complete interval, described the actual amount of sweating in monitor phase. These (MSR, SPA, SWA) values were statistically tried to estimate the sweating difference for any body areas. Based on our results, the average of R and L palms (87.3 ± 4.71, 60.46 ± 2.28, 123.12 ± 10.9, n=12) and the average of R and L soles (78.167 ± 6.128, 42.33 ± 6.6, 133.67 ± 14.61, n=11) were more significant for sweating than chest (44.5 ± 1.87, 23.0 ± 0.89, 99 ± 3.6, n=6) and back (43.7 ± 2.5, 25.16 ± 1.47, 103.5 ± 1.87, n=6). This result was found to be well matching to the actual distribution of sweat gland in body. Therefore, the device with conductivity-based humidity sensing system is practicable in clinical sweat monitoring.",
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A quantitative study for body perspiration with conductivity-based humidity sensing system. / Chang, Bin Wha; Yeh, Shoou Jeng; Tsai, Ping Ping; Chang, Hsien-Chang.

In: Journal of Medical and Biological Engineering, Vol. 21, No. 4, 2001, p. 197-204.

Research output: Contribution to journalArticle

TY - JOUR

T1 - A quantitative study for body perspiration with conductivity-based humidity sensing system

AU - Chang, Bin Wha

AU - Yeh, Shoou Jeng

AU - Tsai, Ping Ping

AU - Chang, Hsien-Chang

PY - 2001

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N2 - The whole measuring system in this study was composed of temperature sensor (a T type of nickel-copper alloy), humidity sensor, flow meter, conductimeter and personal computer. The mini-chip humidity sensor with temperature compensation was fabricated by a conductive poly-(2-acrylamido-2-methyl-propane sulfonate) layer coated on an interdigitated style electrode surface, and was used to detect the slight variation of relative humidity (RH) in a 0.5 ml of closed space. The detection range for RH was 30 to 90 %RH with respect to the conductance response from 1 μS to 85 mS, and the resolution was obtained to be 6 %RH mS-1. This sensor unit was placed on a specific skin surface for sweating monitor and recorded the electrical signal output. Three indexes were characterized for sweating quantification in our experiments. (1) The maximum sweating rate (MSR, %RHmin-1), being used to calculate the first derivative from the sweating data in the first two minute, is acceleration ability for sweat gland to sweating. (2) The partial area of sweating (SPA, %RH min), being used to evaluate the kinetic function of sweating by the SPA obtained from the time with RH value integral in the first two minute. (3) The whole area of sweating (SWA, %RH min), being got from the total area calculation for a complete interval, described the actual amount of sweating in monitor phase. These (MSR, SPA, SWA) values were statistically tried to estimate the sweating difference for any body areas. Based on our results, the average of R and L palms (87.3 ± 4.71, 60.46 ± 2.28, 123.12 ± 10.9, n=12) and the average of R and L soles (78.167 ± 6.128, 42.33 ± 6.6, 133.67 ± 14.61, n=11) were more significant for sweating than chest (44.5 ± 1.87, 23.0 ± 0.89, 99 ± 3.6, n=6) and back (43.7 ± 2.5, 25.16 ± 1.47, 103.5 ± 1.87, n=6). This result was found to be well matching to the actual distribution of sweat gland in body. Therefore, the device with conductivity-based humidity sensing system is practicable in clinical sweat monitoring.

AB - The whole measuring system in this study was composed of temperature sensor (a T type of nickel-copper alloy), humidity sensor, flow meter, conductimeter and personal computer. The mini-chip humidity sensor with temperature compensation was fabricated by a conductive poly-(2-acrylamido-2-methyl-propane sulfonate) layer coated on an interdigitated style electrode surface, and was used to detect the slight variation of relative humidity (RH) in a 0.5 ml of closed space. The detection range for RH was 30 to 90 %RH with respect to the conductance response from 1 μS to 85 mS, and the resolution was obtained to be 6 %RH mS-1. This sensor unit was placed on a specific skin surface for sweating monitor and recorded the electrical signal output. Three indexes were characterized for sweating quantification in our experiments. (1) The maximum sweating rate (MSR, %RHmin-1), being used to calculate the first derivative from the sweating data in the first two minute, is acceleration ability for sweat gland to sweating. (2) The partial area of sweating (SPA, %RH min), being used to evaluate the kinetic function of sweating by the SPA obtained from the time with RH value integral in the first two minute. (3) The whole area of sweating (SWA, %RH min), being got from the total area calculation for a complete interval, described the actual amount of sweating in monitor phase. These (MSR, SPA, SWA) values were statistically tried to estimate the sweating difference for any body areas. Based on our results, the average of R and L palms (87.3 ± 4.71, 60.46 ± 2.28, 123.12 ± 10.9, n=12) and the average of R and L soles (78.167 ± 6.128, 42.33 ± 6.6, 133.67 ± 14.61, n=11) were more significant for sweating than chest (44.5 ± 1.87, 23.0 ± 0.89, 99 ± 3.6, n=6) and back (43.7 ± 2.5, 25.16 ± 1.47, 103.5 ± 1.87, n=6). This result was found to be well matching to the actual distribution of sweat gland in body. Therefore, the device with conductivity-based humidity sensing system is practicable in clinical sweat monitoring.

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