Development of a Smart Clinical Bluetooth Thermometer Based on an Improved Low-Power Resistive Transducer Circuit

Smart sensors have been used in many engineering monitoring and control applications. This work focuses on the development of a new type of clinical Bluetooth thermometer, based on an improved low-power resistive transducer circuit. Most existing resistive transducers use relatively complicated circuits with higher cost and power consumption. To tackle these problems, especially in real applications, an improved low-power resistive transducer circuit is proposed in this work and is used to develop smart Bluetooth thermometers. The parameters of the resistive transducer circuit are selected by quantitative analysis and optimization to improve the performance of the low-power resistive transducer circuit. The effectiveness of the proposed design technology was verified by tests. The temperature measurement error of the new smart Bluetooth thermometer is less than 0.1 °C, which can not only meet the clinical use requirements but also has lower cost and power consumption.


Introduction
Smart transducers/sensors have been used in different engineering applications in manufacturing, system condition monitoring, automatic control, etc. [1,2]. Different from traditional transducers, a smart sensor has built-in functions, such as sensing, preconditioning, detection, monitoring, and information processing, in which a microcontroller unit (MCU) is used as the core processing unit. As illustrated in Figure 1, the outputs from the sensing units are amplified, adjusted, and then converted to digital signals, which are then fed to the MCU for processing. The digital signals can be sent to the receiver by proper wireless communication.

Introduction
Smart transducers/sensors have been used in different engineering applications in manufacturing, system condition monitoring, automatic control, etc. [1,2]. Different from traditional transducers, a smart sensor has built-in functions, such as sensing, preconditioning, detection, monitoring, and information processing, in which a microcontroller unit (MCU) is used as the core processing unit. As illustrated in Figure 1, the outputs from the sensing units are amplified, adjusted, and then converted to digital signals, which are then fed to the MCU for processing. The digital signals can be sent to the receiver by proper wireless communication. According to the measurement principle, the transducers or sensing units could be divided into an inductive mode, capacitive mode, and resistive modes [3]. The inductive transducer uses electromagnetic induction to convert the measured physical quantity into an inductance signal. A capacitive transducer uses a capacitor as a sensing element to convert the measured physical quantity into the change in capacitance. A resistive transducer is a sensing unit to convert the measured physical quantity into the change of resistance values [4]. This work will focus on resistive transducers because of their relatively small size, light weight, simple structure, and fast response speed [5,6].
Currently, the bridge circuit is commonly used in the conversion circuit in the preprocessing unit of smart transducers [7][8][9]. For example, a bridge circuit was used in the development of a textile pressure sensor in a classroom environment [10], which was installed in the fingertips of a glove to measure the pressure variation of each finger when holding an object; the measurement results showed that such a sensor could differentiate the steady-state and the impulse response of a system. In [11], a wearable plantar pressure monitoring system was developed for smart socks, in which a matrix bridge circuit was applied in sock pressure measurement. The pressure sensing matrix was made of conductive fabric and flexible piezo-resistive material [12]. The sensed foot pressure values were digitized and stored in the memory of the sensor-tag, which were then used to monitor the relative pressure of the foot. A non-contact monitoring/inspection smart phone was proposed in [13], based on the vibration characteristics of a beam subjected to thermal stress; a bridge circuit was used for temperature measurement. A simplified PTC circuit was proposed in [14]. It used a dividing voltage with a PTC resistor and fixed resistor to construct a conversion circuit, but it also required an operational amplifier (Op-amp) and many other components in the circuit. A fixed resistor grounding bleeder circuit was proposed in [15]; because it used a fixed resistor on the ground, its power consumption was relatively high (as discussed in Section 2.2.1). Although the aforementioned research results could realize the operation functions, their conversion circuits are either relatively complicated with higher costs or high power consumption, which may not be suitable for battery-powered products [16,17].
The objective of this work was to develop a new type of clinical Bluetooth thermometer, based on an improved low-power resistive transducer circuit. This product will be used for real-time human body temperature monitoring. The following novel aspects are provided in this study: (1) an improved low-power resistive transducer circuit is proposed to reduce cost and power consumption in smart sensor product development; (2) a quantitative method is suggested to optimize the system parameters based on the resolution of the minimal convention circuit and current loss analysis; and (3) a new type of Bluetooth thermometer product is developed for clinical applications. The effectiveness of the proposed circuit and the Bluetooth clinical thermometer was verified by systematic simulation tests.
The remainder of this paper is organized as follows: Section 2 explains the circuit principle of the resistive transducer circuit, and discusses the quantitative optimization of the circuit. Section 3 describes the development of the smart clinical thermometer based on the improved transducer conversion circuit. The effectiveness of the developed smart thermometer is examined using experimental and simulation tests in Section 4.

Bridge Conversion Circuitry
The traditional resistive transducer circuit is mainly based on the use of a bridge conversion circuit [7][8][9], which consists of four resistors: R 1 , R 2 , R 3 , and R X , as illustrated in Figure 2. The resistance values of R 1 , R 2 , and R 3 are fixed, where R X is the resistive transducer (sensing unit) and LM is an Op-amp.
As illustrated in Figure 2, if the power supply (VCC) is V CC , the voltage divider values V 1 and V 2 will be:  Figure 2. A classical bridge conversion circuit. LM is an Op-amp, where "+" and "−" represent the corresponding noninverting and inverting inputs, respectively.
As illustrated in Figure 2, if the power supply (VCC) is CC V , the voltage divider values V1 and V2 will be: If V1 varies with the change of the variable resistor RX and V2 is fixed, the dropout voltage ∆V becomes: With the inputs V1 and V2, the Op-amp output V0 should cover the reference voltage range of the ADC to improve the processing accuracy. For the circuit in Figure 2 , then: The amplified voltage 0 V is inputted to the ADC. If the ADC has N bits, with the reference voltage of VADC and output Do, from Equations (1)-(4), the resistance value of RX can be determined by: When the bridge is balanced or V0 = 0, the measured value of the ADC will be 0. Therefore, in theory, the measurement range of the bridge conversion circuit can cover the whole conversion range of the ADC [18,19]. For example, if the resistance range is 18~51 kΩ, when the resistance is 18 kΩ, the bridge is balanced. When the resistance is 51 kΩ, the measured value of the ADC is close to its full range, or:  If V 1 varies with the change of the variable resistor R X and V 2 is fixed, the dropout voltage ∆V becomes: With the inputs V 1 and V 2 , the Op-amp output V 0 should cover the reference voltage range of the ADC to improve the processing accuracy. For the circuit in Figure 2, if R 4 = R 5 , R 6 = R 7 , the amplification gain of the Op-amp will be A = R 7 R 5 , then: The amplified voltage V 0 is inputted to the ADC. If the ADC has N bits, with the reference voltage of V ADC and output D o , from Equations (1)-(4), the resistance value of R X can be determined by: When the bridge is balanced or V 0 = 0, the measured value of the ADC will be 0. Therefore, in theory, the measurement range of the bridge conversion circuit can cover the whole conversion range of the ADC [18,19]. For example, if the resistance range is 18~51 kΩ, when the resistance is 18 kΩ, the bridge is balanced. When the resistance is 51 kΩ, the measured value of the ADC is close to its full range, or: Given one resistance of R 1 , R 2 , and R 3 , the other two can be obtained from Equations (6) and (7). It can be seen that the bridge conversion circuit is complex with a higher cost.

The Minimal Convention Circuit
The minimal convention circuit consists of components, such as a DC power supply, grounding, a fixed resistor, and a resistive transducer. Its output is directly fed to the ADC but not to an Op-amp. The details are discussed in the following subsections.  Figure 3, a fixed resistor grounding bleeder circuit [15] uses a series connection of the fixed resistor R d and the transducer R X1 . V 01 is the output of this resistive voltage divider.
(6) and (7). It can be seen that the bridge conversion circuit is complex with a higher cost.

The Minimal Convention Circuit
The minimal convention circuit consists of components, such as a DC power supply, grounding, a fixed resistor, and a resistive transducer. Its output is directly fed to the ADC but not to an Op-amp. The details are discussed in the following subsections.

Fixed Resistor Grounding Bleeder Circuit
As illustrated in Figure 3, a fixed resistor grounding bleeder circuit [15] uses a series connection of the fixed resistor Rd and the transducer RX1. V01 is the output of this resistive voltage divider. Given CC V , the following relationships can be obtained: where VADC is the reference voltage of the ADC; R are the respective lower and upper limits of the transducer resistance RX1.
For an ADC circuit, the V01 variation is within the range of the ADC [20,21]. If the ADC has N bits and Do is the ADC output, then: From Equations (8) and (12), the transducer resistance RX1 can be estimated by: where N is the number of bits of the ADC.
As illustrated in Figure 3, the range of V01 is between 0 and VADC. For our designed smart thermometer, if its temperature measurement range is over 25~50 °C , the Given V CC , the following relationships can be obtained: where V ADC is the reference voltage of the ADC; R X1 ∈ [R 1 , R 2 ], R 1 , and R 2 are the respective lower and upper limits of the transducer resistance R X1 . For an ADC circuit, the V 01 variation is within the range of the ADC [20,21]. If the ADC has N bits and D o is the ADC output, then: From Equations (8) and (12), the transducer resistance R X1 can be estimated by: where N is the number of bits of the ADC. As illustrated in Figure 3, the range of V 01 is between 0 and V ADC . For our designed smart thermometer, if its temperature measurement range is over 25~50 • C, the corresponding resistance range will be 18~51 kΩ, or R 1 = 18 kΩ and R 2 = 51 kΩ. If the ADC reference voltage V ADC = 1.2 V, external DC supply voltage V CC = 3.3 V, and R X1 = 18 kΩ, Figure 4 shows the simulation results of the relationship between the output range and current loss of the fixed resistor grounding bleeder from Equations (9)-(11).
corresponding resistance range will be 18~51 kΩ, or ' 1 R = 18 kΩ and ' 2 R = 51 kΩ. If the ADC reference voltage VADC = 1.2 V, external DC supply voltage CC V = 3.3 V, and RX1 = 18 kΩ, Figure 4 shows the simulation results of the relationship between the output range and current loss of the fixed resistor grounding bleeder from Equations (9)-(11). From Figure 4, it can be seen that with the increase in the fixed resistor Rd, the output range of V01 increases. Rd = 0 kΩ corresponds to V01 being grounded. When Rd = 10.28 kΩ, V01 reaches its maximum output. When Rd > 10.28 kΩ, the upper limit of V01 will be greater than the reference voltage VADC of the ADC. The valid output range of V01 will be the difference between VADC and the lower limit of V01. When the lower limit of V01 is equal to VADC, the output V01 will go beyond the range of the ADC. In other words, when Rd = 10.28 kΩ, the measuring range of the ADC is the largest and the conversion accuracy is optimal. Figure 4 also shows the change of the current in mA with respect to the change of Rd. It is seen that the current decreases with the increase of Rd. The measurement accuracy depends on the resolution of the conversion circuit; at the optimum resolution when Rd = 10.28 kΩ, the current is 0.12 mA. Figure 5 shows the proposed low-power circuit. It is a transducer grounding bleeder circuit, where Rf is in series connection with the transducer RX2.

The Proposed Low-Power Circuit
With respect to CC V , the following equations can be obtained:  From Figure 4, it can be seen that with the increase in the fixed resistor R d , the output range of V 01 increases. R d = 0 kΩ corresponds to V 01 being grounded. When R d = 10.28 kΩ, V 01 reaches its maximum output. When R d > 10.28 kΩ, the upper limit of V 01 will be greater than the reference voltage V ADC of the ADC. The valid output range of V 01 will be the difference between V ADC and the lower limit of V 01 . When the lower limit of V 01 is equal to V ADC , the output V 01 will go beyond the range of the ADC. In other words, when R d = 10.28 kΩ, the measuring range of the ADC is the largest and the conversion accuracy is optimal. Figure 4 also shows the change of the current in mA with respect to the change of R d . It is seen that the current decreases with the increase of R d . The measurement accuracy depends on the resolution of the conversion circuit; at the optimum resolution when R d = 10.28 kΩ, the current is 0.12 mA. From Figure 5, the current through this circuit decreases with the increase in RX2, or V02 increases with the increase in RX2.

The Proposed Low-Power Circuit
If the ADC has N bits and Do is the ADC output, then: From Equations (14) and (18), RX2 can be obtained as In our designed smart thermometer, its resistance range is 18~51 kΩ, or ' 3 R = 18 kΩ With respect to V CC , the following equations can be obtained: where R X2 ∈ R 3 , R 4 , R 3 , and R 4 are the respective lower and upper limits of the transducer resistance R X2 . From Figure 5, the current through this circuit decreases with the increase in R X2 , or V 02 increases with the increase in R X2 .
If the ADC has N bits and D o is the ADC output, then: From Equations (14) and (18), R X2 can be obtained as In our designed smart thermometer, its resistance range is 18~51 kΩ, or R 3 = 18 kΩ and R 4 = 51 kΩ, and the measurable temperature range is 25~50 • C. Taking R X2 = 18 kΩ as an example, Figure 6 shows the simulation results of the relationship between the output range and the circuit loss of the transducer grounding bleeder circuit using Equations (15)- (17). From Figure 5, the current through this circuit decreases with the increase in RX2, or V02 increases with the increase in RX2.
If the ADC has N bits and Do is the ADC output, then: From Equations (14) and (18), RX2 can be obtained as In our designed smart thermometer, its resistance range is 18~51 kΩ, or ' 3 R = 18 kΩ and ' 4 R = 51 kΩ, and the measurable temperature range is 25~50 °C . Taking RX2 = 18 kΩ as an example, Figure 6 shows the simulation results of the relationship between the output range and the circuit loss of the transducer grounding bleeder circuit using Equations (15)-(17). It is seen from Figure 6 that with the increase in the resistance of the fixed resistor Rf, the lower limit of V02 is less than VADC, and the valid output range of V02 is the difference between VADC and the lower limit value of V02. When Rf = 89.25 kΩ, the upper limit of V02 equals VADC, and the output of V02 reaches its maximum value. When the lower limit of V02 is equal to VADC, the valid output V02 = 0. When Rf > 89.25 kΩ, the output of V02 decreases. In other words, when Rf = 89.25 kΩ, the measuring range of ADC is the largest and the conversion accuracy is the highest. Furthermore, it is seen in Figure 6 that the current It is seen from Figure 6 that with the increase in the resistance of the fixed resistor R f , the lower limit of V 02 is less than V ADC , and the valid output range of V 02 is the difference between V ADC and the lower limit value of V 02 . When R f = 89.25 kΩ, the upper limit of V 02 equals V ADC , and the output of V 02 reaches its maximum value. When the lower limit of V 02 is equal to V ADC , the valid output V 02 = 0. When R f > 89.25 kΩ, the output of V 02 decreases. In other words, when R f = 89.25 kΩ, the measuring range of ADC is the largest and the conversion accuracy is the highest. Furthermore, it is seen in Figure 6 that the current decreases with the increase in R f . At the optimal resolution, the current is 0.03 mA. Therefore, the power consumption of the proposed low-power circuit is lower than the fixed resistor grounding bleeder circuit.

Development of a Smart Clinical Thermometer
The improved low-power resistive transducer circuit in Section 2.2.2 is implemented for the development of a smart thermometer product for human body temperature monitoring in real-time [22][23][24]. The objective is to develop a new smart clinical thermometer product that is cheaper with lower power consumption. If the temperature exceeds a threshold or the temperature trend is abnormal, the backstage system can provide an early warning of the abnormal situation [25,26].
In this smart thermometer project, because the Bluetooth wireless communication protocol has the advantages of low power consumption, easy use, and a stable link, it is adopted for the data wireless transmission. The Bluetooth chip DA14580 (from Dialog Semiconductor) is selected in this project [27], which has current consumptions of 3.4 mA when sending and 3.7 mA when receiving. It has dedicated hardware for the Link Layer implementation of Bluetooth low-energy and interface controllers to enhance connectivity. The transceiver interfaces with the antenna directly and is fully compliant with the Bluetooth 4.2 standard.
The temperature data is transferred to a computing device (e.g., a cell phone, a computer, a cloud drive) using a general APP with the Bluetooth 4.2 standard. The temperature data can also be transferred to a doctor's office for health diagnosis.
In accordance with the measurement range of 32~42 • C related to human body temperatures, a 3.7 V lithium-ion battery is used as the power source in this smart thermometer [28]. According to the analysis in Section 2.2.2, the transducer grounding divider conversion circuit is applied in this project, as it not only has a more streamlined circuit design than the bridge conversion circuit (Section 2.1), but also lower power consumption than the fixed resistor grounding divider circuit (Section 2.2.1). An NTC thermistor (model 503ET-87L) is used as the resistive transducer [29], which has a high sensitivity, low cost, and small size, with characteristics of B 25/50 = 3950k ± 1%, zero power resistance R 0 = 29.986~30.016 kΩ, and time response = 3.2 s. Corresponding to the temperature measurement range from 32 to 45 • C, its resistance is between 25.292 and 38.137 kΩ. From Equations (15)-(17) with V ADC = 1.2 V, the optimal resistance of the fixed resistor R f is determined as R f = 66.74 kΩ.
The circuit design of the smart thermometer includes the design of the chip peripheral circuit, external flash circuit, temperature conversion circuit, wireless charging circuit, battery power acquisition circuit, and so on. The MCU chip is selected as DA14580 (32-bit ARM Cortex-M0 kernel), with two crystal oscillators at 16MHz (XTAL16M) and 32.768 kHz (XTAL32K), respectively. The 32.768 kHz oscillator is used as the clock of the Extended/Deep Sleep modes. Figure 7 shows the designed peripheral circuit of the MCU.
The DA14580 chip has a built-in 32 KB One-Time-Programmable (OTP) memory, which can be programmed once only, using an extra flash chip W25X20CL [30]. As shown in Figure 8, the W25X20CL serial flash memory can not only provide an extra storage solution, but also a solution with more flexibility and better performance than using an ordinary serial flash device. An SPI protocol is used for the data communication with the chips. Figure 9 shows the designed transducer grounding divider conversion circuit for temperature conversion. The fixed resistor R 1 is selected as 66.74 kΩ (a nonstandard resistance with a nominal value of 66.5 kΩ in E96 1% precision series). C27 is a 0.1 µF ceramic capacitor that is used to reduce the high-frequency interference caused by the instantaneous change of the load current [31]. The ADC is connected to P0.1 pin of DA14580 in Figure 7 to transmit the voltage of T2 to the ADC. The BAT CHECK is connected to P0.2 pin of DA14580 in Figure 7 to detect the power supply voltage.  The DA14580 chip has a built-in 32 KB One-Time-Programmable (OTP) memory, which can be programmed once only, using an extra flash chip W25X20CL [30]. As shown in Figure 8, the W25X20CL serial flash memory can not only provide an extra storage solution, but also a solution with more flexibility and better performance than using an ordinary serial flash device. An SPI protocol is used for the data communication with the chips.    The DA14580 chip has a built-in 32 KB One-Time-Programmable (OTP) memory, which can be programmed once only, using an extra flash chip W25X20CL [30]. As shown in Figure 8, the W25X20CL serial flash memory can not only provide an extra storage solution, but also a solution with more flexibility and better performance than using an ordinary serial flash device. An SPI protocol is used for the data communication with the chips.  temperature conversion. The fixed resistor R1 is selected as 66.74 kΩ (a nonstandard resistance with a nominal value of 66.5 kΩ in E96 1% precision series). C27 is a 0.1 µ F ceramic capacitor that is used to reduce the high-frequency interference caused by the instantaneous change of the load current [31]. The ADC is connected to P0.1 pin of DA14580 in Figure 7 to transmit the voltage of T2 to the ADC. The BAT CHECK is connected to P0.2 pin of DA14580 in Figure 7 to detect the power supply voltage. To reduce the dimension of the smart thermometer for the convenience of application, a lithium-ion battery (model 401119) is selected as the power source for the circuit, whose battery capacity is 100 mAh. To facilitate application, the battery can be recharged wirelessly. QX4054 (from Qxmd) [32] is selected as the battery recharging chip, which is a constant current and constant voltage linear charging chip. QX4054 has an internal MOSFET structure, which is suitable for portable applications. Figure 10 shows the battery charging circuit. The charging coil and the 33 nF capacitor form an inductance-capacitance (LC) resonant circuit to charge the lithium-ion battery.  To reduce the dimension of the smart thermometer for the convenience of application, a lithium-ion battery (model 401119) is selected as the power source for the circuit, whose battery capacity is 100 mAh. To facilitate application, the battery can be recharged wirelessly. QX4054 (from Qxmd) [32] is selected as the battery recharging chip, which is a constant current and constant voltage linear charging chip. QX4054 has an internal MOSFET structure, which is suitable for portable applications. Figure 10 shows the battery charging circuit. The charging coil and the 33 nF capacitor form an inductance-capacitance (LC) resonant circuit to charge the lithium-ion battery. temperature conversion. The fixed resistor R1 is selected as 66.74 kΩ (a nonstandard resistance with a nominal value of 66.5 kΩ in E96 1% precision series). C27 is a 0.1 µ F ceramic capacitor that is used to reduce the high-frequency interference caused by the instantaneous change of the load current [31]. The ADC is connected to P0.1 pin of DA14580 in Figure 7 to transmit the voltage of T2 to the ADC. The BAT CHECK is connected to P0.2 pin of DA14580 in Figure 7 to detect the power supply voltage. To reduce the dimension of the smart thermometer for the convenience of application, a lithium-ion battery (model 401119) is selected as the power source for the circuit, whose battery capacity is 100 mAh. To facilitate application, the battery can be recharged wirelessly. QX4054 (from Qxmd) [32] is selected as the battery recharging chip, which is a constant current and constant voltage linear charging chip. QX4054 has an internal MOSFET structure, which is suitable for portable applications. Figure 10 shows the battery charging circuit. The charging coil and the 33 nF capacitor form an inductance-capacitance (LC) resonant circuit to charge the lithium-ion battery.  Figure 10. The lithium-ion battery recharging circuit. Figure 10. The lithium-ion battery recharging circuit.
In the PCB design, considering the special design requirements of a small PCB size and high device density, special considerations are undertaken in the PCB layout and wiring design to reduce the influence of distributed inductance, EMC, and crosstalk. The design also involves Bluetooth antennas, charging coils, component layouts, etc. Figure 11 depicts the 2-layer PCB of this developed smart thermometer. Figure 12 shows a prototype of the developed smart clinical thermometer product, where the screen can display the body temperature and other related monitoring information (e.g., system control setup, time period for recording, alarming, Bluetooth transmission set-up). and high device density, special considerations are undertaken in the PCB layout and wir-ing design to reduce the influence of distributed inductance, EMC, and crosstalk. The design also involves Bluetooth antennas, charging coils, component layouts, etc. Figure 11 depicts the 2-layer PCB of this developed smart thermometer. Figure 12 shows a prototype of the developed smart clinical thermometer product, where the screen can display the body temperature and other related monitoring information (e.g., system control setup, time period for recording, alarming, Bluetooth transmission set-up).  There are several types of Bluetooth thermometers on the market, such as the Bluetooth thermometer TWJ [33] and Children's thermometer BLE 4.0 [34]. The main control chip of TWJ is AMICCOM A8105 [35]. Although AMICCOM A8105 does not need an extra flash chip, it is more expensive than DA14580 and W25X20CL as used in this project. In addition, these available thermometers adopt a bridge conversion circuit connected with an Op-amp, which has a higher cost. On the other hand, the main control chip of BLE 4.0, CC2540 [36], requires an extra flash chip and a bridge circuit connected with an Op-amp. Correspondingly, the designed thermometer in this project is cheaper than most of these available thermometers. and high device density, special considerations are undertaken in the PCB layout and wiring design to reduce the influence of distributed inductance, EMC, and crosstalk. The design also involves Bluetooth antennas, charging coils, component layouts, etc. Figure 11 depicts the 2-layer PCB of this developed smart thermometer. Figure 12 shows a prototype of the developed smart clinical thermometer product, where the screen can display the body temperature and other related monitoring information (e.g., system control setup, time period for recording, alarming, Bluetooth transmission set-up).  There are several types of Bluetooth thermometers on the market, such as the Bluetooth thermometer TWJ [33] and Children's thermometer BLE 4.0 [34]. The main control chip of TWJ is AMICCOM A8105 [35]. Although AMICCOM A8105 does not need an extra flash chip, it is more expensive than DA14580 and W25X20CL as used in this project. In addition, these available thermometers adopt a bridge conversion circuit connected with an Op-amp, which has a higher cost. On the other hand, the main control chip of BLE 4.0, CC2540 [36], requires an extra flash chip and a bridge circuit connected with an Op-amp. Correspondingly, the designed thermometer in this project is cheaper than most of these available thermometers. There are several types of Bluetooth thermometers on the market, such as the Bluetooth thermometer TWJ [33] and Children's thermometer BLE 4.0 [34]. The main control chip of TWJ is AMICCOM A8105 [35]. Although AMICCOM A8105 does not need an extra flash chip, it is more expensive than DA14580 and W25X20CL as used in this project. In addition, these available thermometers adopt a bridge conversion circuit connected with an Op-amp, which has a higher cost. On the other hand, the main control chip of BLE 4.0, CC2540 [36], requires an extra flash chip and a bridge circuit connected with an Op-amp. Correspondingly, the designed thermometer in this project is cheaper than most of these available thermometers.

Testing and Analysis of the Improved Transducer Grounding Bleeder Circuits
Based on the specific measurement requirements, the optimal resistance value of the fixed resistor can be determined using the method discussed in Section 2.2. Four commonly used ADCs with 8, 10, 12, and 16 bits are considered. Figure 13 shows the relationship between the ADC outputs and the resistance of the resistive transducer R X . It also demonstrates the comparison results among the three grounding circuits: (1) the classical bridge conversion circuit, (2) the fixed resistor grounding bleeder circuit, and (3) the transducer grounding bleeder circuit. Table 1 summarizes the comparison results of these three circuits. fixed resistor can be determined using the method discussed in Section 2.2. Four commonly used ADCs with 8, 10, 12, and 16 bits are considered. Figure 13 shows the relationship between the ADC outputs and the resistance of the resistive transducer RX. It also demonstrates the comparison results among the three grounding circuits: (1) the classical bridge conversion circuit, (2) the fixed resistor grounding bleeder circuit, and (3) the transducer grounding bleeder circuit. Table 1 summarizes the comparison results of these three circuits.  Based on the above demonstrated results, the following conclusions can be drawn: (1) The ADC outputs differ with the ADC bits (N = 8, 10, 12, and 16 bits).
(2) By using the improved conversion circuit, the output of the transducer grounding divider conversion circuit has a positive correlation with the increase in the transducer resistance, which is better than the fixed resistor grounding divider conversion circuit, which has a negative correlation with the increase in the transducer resistance.
(3) The ADC output of the proposed transducer grounding divider conversion circuit (red line) is also higher than that of the classical bridge conversion circuit (black line).  Based on the above demonstrated results, the following conclusions can be drawn: (1) The ADC outputs differ with the ADC bits (N = 8, 10, 12, and 16 bits).
(2) By using the improved conversion circuit, the output of the transducer grounding divider conversion circuit has a positive correlation with the increase in the transducer resistance, which is better than the fixed resistor grounding divider conversion circuit, which has a negative correlation with the increase in the transducer resistance.
(3) The ADC output of the proposed transducer grounding divider conversion circuit (red line) is also higher than that of the classical bridge conversion circuit (black line).
(4) The resolution of the transducer grounding bleeder circuit is approximately the same as the fixed resistor grounding bleeder circuit, but its power consumption is lower than that of the fixed resistor grounding bleeder circuit.
(5) Given an ADC with specific bits, although the measurement resolution of the thermometer based on the resistive divider conversion circuit could be lower than that based on the classical bridge conversion circuit, its resolution can be improved by using a higher-bit ADC. For example, the measurement resolution of a 12-bit ADC for the resistive divider conversion circuit (i.e., 1.18 × 10 −2 • C) is about 2 times higher than that of the traditional bridge conversion circuit using a 10-bit ADC (i.e., 2.55 × 10 −2 • C). Meanwhile, when the ADC has 12 bits or higher, its measurement resolution can meet the requirements of this clinical thermometer while its circuit is more streamlined and is cheaper in cost. Figure 14 shows the experimental set-up used to examine the accuracy of the developed smart thermometer product. The NTC thermistor is replaced by a DC resistor device. In testing, the leading wires should be as short as possible to reduce the influence of the wire resistance on the experiment results. same as the fixed resistor grounding bleeder circuit, but its power consumption is lower than that of the fixed resistor grounding bleeder circuit.

Test and Analysis of the Smart Thermometer System
(5) Given an ADC with specific bits, although the measurement resolution of the thermometer based on the resistive divider conversion circuit could be lower than that based on the classical bridge conversion circuit, its resolution can be improved by using a higherbit ADC. For example, the measurement resolution of a 12-bit ADC for the resistive divider conversion circuit (i.e., 1.18 × 10 −2 °C ) is about 2 times higher than that of the traditional bridge conversion circuit using a 10-bit ADC (i.e., 2.55 × 10 −2 °C ). Meanwhile, when the ADC has 12 bits or higher, its measurement resolution can meet the requirements of this clinical thermometer while its circuit is more streamlined and is cheaper in cost. Figure 14 shows the experimental set-up used to examine the accuracy of the developed smart thermometer product. The NTC thermistor is replaced by a DC resistor device. In testing, the leading wires should be as short as possible to reduce the influence of the wire resistance on the experiment results. The experimental tests cover the general temperature range of 32~42 °C . The one-toone correspondence between the body temperature value and the theoretical resistance value can be established by calibration. Figure 15 demonstrates the experimental results. The upstroke temperature and the downstroke temperature are the mean values over 10 simulation tests, where upstroke refers to the change in the output as the input increases and the downstroke denotes the change in the output as the input decreases. All of the tests and measurements have followed the regulations in accordance with the National Standards of Clinical Electronic Thermometer GB/T 21416 in China. The temperature measurement range and the maximum permissible errors of the thermometers are listed in Table 2. It can be seen that the tested temperature errors in Figure 15 are less than those regulated by GB/T 21416 in China, thus the developed smart clinical thermometers can meet the requirements (they have become commercial products in China). The experimental tests cover the general temperature range of 32~42 • C. The one-toone correspondence between the body temperature value and the theoretical resistance value can be established by calibration. Figure 15 demonstrates the experimental results. The upstroke temperature and the downstroke temperature are the mean values over 10 simulation tests, where upstroke refers to the change in the output as the input increases and the downstroke denotes the change in the output as the input decreases. All of the tests and measurements have followed the regulations in accordance with the National Standards of Clinical Electronic Thermometer GB/T 21416 in China. The temperature measurement range and the maximum permissible errors of the thermometers are listed in Table 2. It can be seen that the tested temperature errors in Figure 15 are less than those regulated by GB/T 21416 in China, thus the developed smart clinical thermometers can meet the requirements (they have become commercial products in China).

Conclusions
A new type of clinical Bluetooth thermometer product was developed in this work for real-time clinical body temperature measurement and monitoring. An improved lowpower resistive transducer circuit was proposed to simplify the circuit design and to reduce the product cost and power consumption. A quantitative analysis method was proposed to optimize the circuit parameters to improve system performance. The effectiveness of the improved conversion circuit technology was verified by experimental tests. The test results show that the transducer grounding divider conversion circuit outperforms the fixed resistor grounding divider conversion circuit and the classic bridge circuit. In addition, the developed smart thermometer can meet the requirements of clinical measurement applications, with a more streamlined circuit design, lower cost, and lower power consumption.
Funding: This research received no external funding.

Institutional Review Board Statement:
The study did not require ethical approval.

Informed Consent Statement:
The study did not involve humans.

Data Availability Statement:
The study did not report any data.

Conflicts of Interest:
The authors declare no conflict of interest.

Conclusions
A new type of clinical Bluetooth thermometer product was developed in this work for real-time clinical body temperature measurement and monitoring. An improved lowpower resistive transducer circuit was proposed to simplify the circuit design and to reduce the product cost and power consumption. A quantitative analysis method was proposed to optimize the circuit parameters to improve system performance. The effectiveness of the improved conversion circuit technology was verified by experimental tests. The test results show that the transducer grounding divider conversion circuit outperforms the fixed resistor grounding divider conversion circuit and the classic bridge circuit. In addition, the developed smart thermometer can meet the requirements of clinical measurement applications, with a more streamlined circuit design, lower cost, and lower power consumption.