TWI306023B - Monitoring apparatus for physical movements of a body organ and method for acouiring the same - Google Patents

Description

1306023 IX. Description of the Invention: [Technical Field] The present invention relates to a monitoring device for physical activity of a human organ and a method for capturing the same, and particularly relates to an ultra wideband electromagnetic wave (UWB) detection using an ultra wideband electromagnetic wave (UWB) A monitoring device for the physical activity of human organs and a method of capturing it. [Prior Art]

The primary purpose of using a monitoring instrument to monitor a patient's vital signs (such as heartbeat, pulse, etc.) is to alert the patient or his caregiver to an abnormal cardiovascular condition. The pulse monitoring systems and techniques currently used on patients are mostly on the pulse vessels of the human body, and the desired physiological signals are extracted by piezoelectric/pressure sensors. US 4,489,73 1 discloses a technique for detecting sonic chatter caused by pulse pulsation using a piezoelectric crystal. No. 5,759,300 discloses an element comprising a pressure sensor that can be placed on the radial artery of the wrist surface near the thumb (ie parallel to the finger belt) for better signal to noise ratio . Most techniques for monitoring heartbeat use shh electrodes to extract electrocardigram signals. In the above prior art, the pressure sensor or skin electrode must be pressed against the patient. The skin's in order to get good measurement signal quality. Lack of 'long-term squeezing of skin tissue may cause discomfort to the patient, may also cause skin irritation, inflammation and sweating, and thus retreat, resulting in a decrease in signal noise ratio and a baseline shift in the signal. Wave detection of the heart and lungs US 5,759,012 discloses a measuring element using ultra-wideband electromagnetic 1306023 and vocal cord activity. The measuring component uses a non-acoustic pulse wave radar operating in a repetitive mode to average a plurality of reflected pulse waves. The measuring component employs a range delay generator that generates a time gating pulse by a time gate scheme. At this time, the brake pulse wave causes the receiving path to be selectively turned on, and the reflected pulse wave reflected by the human body is received by the receiver antenna. The measuring component converts the detected voltage into an audible audio signal using amplitude modulation and a Doppler effect. In addition, the measuring element is designed for distal operation and therefore cannot be worn on a patient undergoing testing. Therefore, it is not suitable for use in portable long-term monitoring. In view of the above problems, the industry does require a monitoring device that can be worn on a patient, provides long-term stable operation characteristics, and has small physical activities of human organs at a low price. [Summary of the Invention]

The monitoring device of the physical activity of the official and its extraction method. In order to achieve the above object, the present invention provides a physical activity of a human body organ

A plate, a type of plate, a digital plate, and a radiatable UWB electromagnetic wave (detecting pulse wave) and an analog signal for receiving physical activity of the plurality of electronic components through the human organ. The digital signal is converted into a digital signal 100210 106071 005366837 • 8· 1306023. The display element can display the physical activity state of the human organ. In particular, the electronic components of the analog panel comprise a first pulse generator, a second pulse generator and a balanced mixer. The first pulse generator is configured to generate the detection pulse wave, and the second pulse wave generator is configured to generate a reference pulse wave. The second pulse wave generator is electrically connected to one of the balanced wave mixers. The first input port is electrically connected to the second input port of the balanced mixer for generating a phase difference signal representative of the physical activity of the human body. The method for extracting the physical activity of the human organ of the present invention firstly emits a series of ultra-wideband UWB electromagnetic waves (detecting pulse waves) to the human body to measure the detected pulse wave of the physical activity scattering of the human body and a reference pulse wave. The phase difference between Ap: = A milk A A 2 = c M = VTa / represents the frequency of the detected pulse sequence, c represents the speed of light, £ represents the relative dielectric constant of the skin tissue of the human body, and r represents the body organ The moving speed of the physical movement of the detected pulse direction, Γα, represents the time when the human organ moves a predetermined distance button. Therefore, the physical activity μ of the human organ is linearly proportional to △ Shanghai. [Embodiment] Figs. 1(a), 1(b) and 1(c) illustrate that the monitoring device 1 of the present invention is worn somewhere on the human body to detect cardiovascular physical activity. However, the monitoring device 10 obviously also has the possibility of other applications. For example, the monitoring device ίο can also be worn on other parts of the human body, including the back of the chest. 100210 1〇β〇7ΐ 0053668^7 -9- 1306023 Dirty 'fetus, vocal cords and muscles. For the sake of simplicity, the following uses physical activity monitoring of the blood vessels as an embodiment. The monitoring device 10 can be worn on the patient's body without applying a force by a belt 12'.

2(a) and 2(b) illustrate the monitoring device 10 of the present invention. As shown in Fig. 2(a), the monitoring device 10 includes an antenna board 23, an analog board 24, and a digital board 25. The antenna plate 23 can emit electric waves to an artery 26 and receive its reflected waves. The antenna board 23 includes a transmitting antenna 21 and a receiving antenna 22. The transmitting antenna 21 and the receiving antenna 22 respectively transmit a detecting pulse wave and a detecting pulse reflected by the human body via a film 20. The transmitting antenna 2 i and the receiving antenna 22 may be a bow-tie antenna as shown in Fig. 2(b). The film 20 is not used to convert signal energy and is only one of the integral components of the monitoring device. Therefore, the material properties of the film 20 should not cause energy attenuation of the detecting pulse wave. Preferably, the film 2 is made of a polymer material (for example, a resin synthetic rubber or poly having a thickness of 0.2 to 0.5 mm). Carbonate Figure 3(a) shows the clock map of the detected pulse wave. Each probe pulse wave is composed of a damped sinusoidal oscillation whose resonance frequency depends on the physical size of the transmitting antenna. (13) showing a spectrogram of the detected pulse wave. The center frequency and bandwidth of the detected pulse wave are determined by the duration of the sinusoidal fluctuation of the decay. When the duration of the sinusoidal fluctuation is approaching zero (for one) In the ideal pulse shape, the bandwidth of the center frequency and the frequency spectrum approaches infinity. In Fig. 4, a functional block diagram of the monitoring device 1 is shown. The transmitting antenna 21 and the receiving antenna 22 are Set on the antenna board 23, and both are bow-tie days

The line 'is one of the broadband dipole antennas.兮 100210 1〇6〇71 005366837 -10- 1306023

The analog board 24 includes a balanced mixer 4 connected to the receiving antenna 22, a high pass filter 5 connected to the balanced mixer 4, a first low pass filter 6 connected to the high pass filter 5, a first amplifier 7 connected to the low pass filter 6, a second low pass filter 8 connected to the first amplifier 7, a second amplifier 9 connected to the second low pass filter 8, and a a first pulse generator 15 connected to the balanced mixer 4, a delay line 14 connected to the first pulse generator 15, a second pulse generator 16 connected to the transmitting antenna 21, and a connection The second pulse generator 16 and the clock generator 2 of the delay line 14 are connected. The tablet 25 includes a microcontroller 18 having an embedded analog/digital converter 17 and a general purpose non-synchronous wireless transceiver 丨9. The human tissue surrounding the arterial blood vessel 26 can reflect the detection pulse wave to form an imaginary signal component, and the analog signal processing circuit on the analog plate 24 selectively separates the physics representing the arterial blood vessel 26 from the signal component. Activity signal. The microcontroller 18 digitizes the detected signal and transmits the digitized signal via the wireless transceiver 15> of the tablet 25. The digitized signal can be transmitted to an external data processing/display unit 28 via an RS232 or USB cable 27. The UWB electromagnetic wave system of the present invention considers the following advantages: 1 · UWB electromagnetic wave can reduce the spectral density of the dissipated power. Electromagnetic wave dissipation affects doctors and patients, and the use of UWB electromagnetic waves not only reduces the power dissipation, but also avoids electromagnetic interference with other medical devices in the hospital. 2. Reduce the overall volume of the instrument.

3. Reduce the occurrence and impact of external interference, and increase the reliability of measurement 100210 1〇6〇71 005366837 •11- 1306023 degrees. As with the construction of a common narrow-band radar, the monitoring device ι〇 of the present invention uses electromagnetic waves to scatter characteristics of two age boundaries having different scattering parameters, and the setting of the material parameters is based on well-known theory. The electromagnetic wave radiated by the radar is scattered by the moving object, and the shock frequency of the scattered pulse wave is changed by the effect of the material. The change of the frequency causes the earthquake blue to change, and the number of earthquakes in the scattered pulse wave remains. The same number. Thus, the interval 散射 of the scattered pulse wave changes. Due to the same effect, the repetition frequency of the electromagnetic wave scattered by the object κ and the corresponding repetition period will also change at the same time. The characteristics of these changes depend on the direction of movement of the target to be measured relative to the radar, and the value of the change depends on the radial speed of the target to be measured. However, it must be noted that the UWB radar is used to detect and measure the parameters of the moving target, which uses certain characteristics. In the general case, all three parameter variations of the pulse sequence mentioned above are used in order to separate a particular signal. However, the frequency-synchronization phase # of the single-scattered pulse wave is small because the interval 7 of the single-scattered pulse wave is very short. For example, for a pulse interval of 1. 2 nanoseconds, it does not contain any-cycles with a seismic frequency of 1 GHz. It is impossible to determine the frequency variation of a single scattered pulse wave using the conventional filtering technique. However, measuring the phase difference between a series of scattered pulse waves and the detected pulse wave is awkward. The phase difference can be estimated according to the following formula. When an object moves toward the radar at a pre-twisting speed K, the repetition period of the scattered pulse wave becomes 100210. 1〇6〇71 005366837 -12- (1) 1306023 τ〇=τ 1-Γ c represents the speed of light. The phase difference and its variation characteristics during the movement of the object can be determined according to the following equation. If the instantaneous phase value of the detected pulse wave is V 2 , where y represents the repetition frequency of the detected pulse wave. The instantaneous phase value of the detected pulse wave scattered by the fixed object set at the position R is: (Ρ〇^)=φα{ή+2π·/~ = 2π^ + ~] , c K c J (2) The phase difference between the detecting pulse wave and the scattered pulse wave can be expressed as follows: - aroma (3) The phase difference between the detecting pulse wave and the scattered pulse wave caused by the physical activity of the arterial blood vessel 26 can be derived according to equation (3). Got it. If the arterial line 26 is located at a distance A + A, where A indicates the distance between the surface of the antenna plate and the surface of the skin 13 'A' indicates the distance between the surface of the artery and the surface of the skin 13, The instantaneous phase value of the scattered pulse wave is ι(ρ0+ρ^) t + jPo+D^)' (4) (5) The phase difference between the detected pulse wave and the scattered pulse wave is: Δ^1 = < Pu (ή~φοι (t) = -4π · If the arterial blood vessel 26 moves to a position far from the radar, the instantaneous phase value of the scattered pulse wave is: Ψ〇2 (ή = <Ρα+2π· = 2 (p〇+ AV^y (6) The phase difference between the detection pulse wave and the scattering pulse f can also be expressed as follows ^Ψι = Ψη W- <Ρ〇2 (ή = -4π ι〇〇2ΐ〇106071 〇〇 53668q7 -13- (7) 1306023 Equation (5) minus equation (7), the phase difference caused by the movement of the artery 26 can be obtained as follows: Αφ (ή = Αφι-Αφ2 = (8) So, each The phase difference of the period is different, and the trend of the change varies with the moving speed of the artery 26 and the moving period of the oscillation. If the frequency of the pulse is repeated /= 10 million Hertz (MHz), f=4〇, and the physical movement amount of the artery 26 is gA_A=2〇mm, then the phase difference is changed by Δ·0.3·3 degrees. The above data can use the ready-made phase measuring component. The operation of the monitoring device 10 will be described in detail below. Figures 5(a), 5(b), 5(c) and 5(d) are circuit diagrams of the analog board 24 of the present invention. The generator 2 is implemented by a logic inverter 102. The clock generator 2 generates a square wave 'and synchronizes the analog signal processing circuit of the analog plate 24. The clock generator 2 The accuracy of the clock depends on a quartz crystal 1 〇 3. The low-cost quartz crystal will have an error. The resistor 1〇4 can buffer the sharp logic level transition of the quartz crystal 103 and avoid the parasitic oscillation mode. The combination of the valley 105 and the valley 106 can constitute an approximate load capacitance, as stated in the specification of the quartz crystal 103. The resistance 1 〇 4 is at a critical value or at a mean value for a resistive negative feedback. The inverter 102 is voltage-controlled and provides an AC feedback through the core crystal 103 to control the oscillation frequency. The second pulse generator 16 (which can be regarded as a shape detector for detecting the pulse wave of the transmitter) formed by the phase detector 108 and the logic inverter 1〇9 is connected to the transmitting antenna 21. One of the transmitting antennas 21 is intermittent The edge of the vibrator is connected to a pull-up resistor 220 (50 ohms), which is used to reduce the time interval of the 1302063 of the transmitting antenna 21 (or the time interval of the clock signal is entered via a buffer). A receiver circuit 'and the buffer is implemented by a logic inverter 32. The logic inverter 32 reduces the effects of the receiver on the operation of the transmitting circuit and the clock generator 2. The reference pulse wave is generated from the delayed clock signal of the clock generator 2, and is modified into a shorter pulse wave by the first pulse generator 15, and then transmitted to the contact of the resistor 35 and the resistor 36. The pulse generator 15 is composed of a logic inverter 33, a capacitor 34, and resistors 35, 36. The delay line 14 is used to match the timing between the detection pulse wave and the reference pulse wave, so that the balanced mixer 4 can correctly measure the phase difference between the two, wherein the delay line 丨4 is controlled by a variable The resistor 43 and a capacitor 44 are formed. The time delay of the reference pulse wave (U can be determined according to the following equation: ^, = 2 (J7 + 7l 'VJ) (9) where £> represents the distance between the surface of the antenna plate 23 and the skin 13. a represents the distance between the artery 26 and the skin 13. c represents the speed of light, and the relative dielectric constant of the human skin tissue is shown in Table | As shown in Fig. 5(a), where RC is the variable resistor The product of the resistance value of 43 and the capacitance value of the capacitor 44 constitutes the delay line 14. In particular, the value of the resistor 43 can be adjusted by adjusting the resistance value of the variable resistor 43. The reflected pulse wave is reflected. After receiving the receiving antenna 22, it continues to enter the input point of the balanced mixer 4. The resistive loads 30, 31 are matched loads of the symmetric receiving antenna 22. Figure 6(a) and Figure 6(b) illustrate the balanced mixer The operation mode of 4. In the positive half cycle of the reference pulse wave, the diodes VD2 and VD3 are both turned on, and the detected pulse wave transmitted to the balanced mixer 4 is transmitted to the 100210 106071 005366837 -15-1306023. The output end, as shown in Figure 6 (4), is in the negative half cycle of the reference pulse wave, and the diodes are turned on. The detection pulse wave is transmitted to the output # of the balanced mixer 4 at a phase shift of -18 degrees, as shown in Fig. 6(b). The output voltage of the balanced mixture can be defined by the following equation: UWAD = R (lmi - Ivda)+R(Ivdi ~ IW3) ( i 0 )

Where π represents the resistance value of the resistor 35 and the resistor 36. The voltage-current characteristics of the diode can be estimated by a third-order polynomial: ^νϋ=α〇+ αλυ + a2U2 + a3U3 In the above equation (10), the following two equations can be obtained: (11) (12) r (Ivdi -Im4) = 2R -^ + la2 ^-Uw+a3^- + 3a3U2w / 2 2 > Also 2 - U = 2 7 A ¥ + 2a2 $Uio - a humiliation - 3 said. Adding equations (11) and (12), you can get:

^load = 4i?a2C/fifULO (13) Equation (13) shows that the balanced mixer 4 achieves multiplication of the received detection pulse ί^ with the reference pulse Uw. Fig. 7(a) shows the detection pulse wave & and the reference pulse wave received by the balanced mixer 4, wherein the detected pulse wave system is indicated by a solid line, and the reference pulse wave is indicated by a broken line. When the arterial blood vessel 26 is moved toward or away from the monitoring device 10, the corresponding time variation of the phase difference shown in Fig. 7(a) produces a positive pulse and a negative at the output of the balanced mixer 4 as shown in Fig. 7(b). Pulse wave. In summary, the output of the first low pass filter 6 will produce an output signal. Figure 8 (a)

100210 005366837 • 16· 1306023 The vascular vibration state and FIG. 8(b) further compare the timing diagram of the arterial blood vessel 26 of the artery in a resting state. . The output pulse of the balanced mixer 4 continues to be passed to the first low pass filter 6, which filters out unwanted high frequency portions to produce the desired turn (7). As shown in Fig. 9, the line of the rate of the employee's heart is the integer frequency of the repetition frequency of the received pulse wave and the repetition frequency of the reference pulse wave. The first low pass filter 6 filters out high frequency components ("±±^) other than the signal (F), and

A line of frequency F (which can be seen as a signal modulated by the physical activity of the arterial vessel) is selected. The balanced mixer 4 allows for greater precision in the multiplication between the input signal and the reference pulse. In other words, a mixer output signal with significantly reduced distortion is available. The balanced circuit structure allows a high isolation of an input signal (from the antenna) and a reference pulse signal, and highly isolates the input signal from the output signal of the mixer (the average value of the insulation is 4 〇 decibels (dB)). Therefore, the reference pulse of the balanced mixer 4 and the radiation penetration of the receiving antenna 22 can be reduced. Referring to Fig. 5(a), a high-pass filter 5 composed of a capacitor 41 and a capacitor 42 removes a direct current (DC) component which is generated by the surrounding stationary tissue of the artery 26. A first low pass chopper 6 comprising a resistor 38, a capacitor 40, a resistor 37 and a capacitor 3 9 is used to select a low frequency signal corresponding to the physical activity of the arterial vessel 26.

As shown in Fig. 5(b), the first amplifier 7 composed of a first stage amplifying unit (a low frequency instrument amplifier) and a second stage amplifying unit amplifies the low frequency signal. The gain of the first-stage amplifying unit can be set to 117.27 (41.38 dB) by adjusting the resistance value of the resistor 51. The first stage amplifying unit also suppresses the common mode 100210 106071 ΟΟ5366837 -17- 1306023 interference not less than 110 decibels. The signal then enters the second stage amplifying unit, which is based on operational amplifiers 71 and 72. The gain of the second stage amplifying unit can be determined by the following equation: K2 • R(72iy '100^0^' R(722) _ \OKOhm _ —10 (20dB) The resistance value of the resistor 723 can be determined by the following equation: And (723)=—U9. Call v 7 R(72l) + R(722) 110

Referring to Figure 5(c), the amplified signal enters a second low pass filter 8 based on operational amplifiers 73 and 74, which is a 4th order Butterworth active filter. This type of filter provides the most uniform frequency response in the passband. The filtered signal enters a third stage amplifying unit which is located in a second amplifier 9 which is based on the operational amplifier 75. The gain of the third stage amplifying unit can be set by adjusting the resistor 751 and the resistor 752, and the gain can be determined by the following formula:

K3 [and (751)] ' AJkOhm, U(752)J, 2k0hm > -2.35 (7.4dB) The overall gain of the receiver is equal to: K = ΚλΚ2Κ3 = (117.28) -(10)- (2.35) = 2756.08 ( 68.8dB) Referring to FIG. 5(d), an operational amplifier 80 buffers a voltage divider to generate a virtual ground. This circuit produces a virtual ground reference voltage at 1/2 of the supply voltage. The circuit includes a compensation mechanism to allow bypass capacitors 801, 52, 724, and 753 to be provided at the virtual grounded output. The benefits of large capacitors are not only virtual grounding, but also a very low direct current (DC) impedance to the load, and its alternating current (AC) impedance is also very high.

100210 1〇6〇71 ΟΟ5366837 -18- 1306023 Low. The op amp 80 can sink and discharge more than 5 mA, which improves the recovery time of the transient time of the load current. Figure 11 illustrates a circuit diagram of the tablet 25 of the present invention. After amplification and filtering, the subsequent signal is transmitted from the analog board 24 by a connector 76 (refer to FIG. 5(C)) to an analog/digital converter embedded in the microcontroller 18. The microcontroller 18 is preferably a reduced instruction set processor (Reduced Set)

Computer, RISC) architecture 8-bit low-power (^〇8 microcontroller, in fact, the data collection and data transmission from analog signal processing circuit is available. Data transmission can be done by RS-232 or USB interface. The serial port driver 78 is connected to the tablet 25 via an RS-232 interface, and has an external data processing and display unit 28. The transmitter 19 and the electronic erasable memory (4) communicate via a USB interface. It can be a USB single-chip universal non-synchronous transceiver, which transmits a series of data with a data transfer rate of 920 kbaud (baud). The electronic erasable memory is used to store structural parameters. The USB vendor identifier, the product identifier, the sequence 1 and the controller string are included. The reference voltage source of the three-terminal adjustable shunt regulator 79 is used to supply the analog signal processing of the analog board 23. The reference voltage of the circuit and the analog/digital converter of the microcontroller of the tablet 25. Referring to Figure 10, the improvement in energy performance of the monitoring device 1 is due to the signal amplitude spectrum 220 entering the transmitting antenna 21 and The frequency of the antenna 21 is matched by the efficiency U0. Therefore, the radiated signal energy is almost twice that of the common component (with the signal spectrum packet 120 and the same antenna frequency performance). The match between the signal amplitude spectrum and the antenna frequency performance The selection of a suitable transmitting antenna, such as a loop antenna (1〇〇p antenna), a collared antenna end 1306023, a terminating half-wave antenna, and a spiral antenna, respectively, is shown in Figure 12(4). 12(b), 12(.), and 12(4) FIG. 13(a) and FIG. 13(b) show a comparison diagram of the sfl-number waveform and the electrocardiogram signal waveform of the radial artery captured by the monitoring device 1. As shown in Fig. 13(b), the performance of the monitoring device 10 can be confirmed in a clinical device by comparing the radial artery pulse signal 2〇〇 and the electrocardiogram 210 obtained by the monitoring device. a) The displayed waveform is taken from a patient with a normal heartbeat rhythm. Conversely, the waveform shown in Figure 13(b) is from a patient with arterial premature c〇ntracti〇n 'Apc' symptoms. Both results show a fairly clear heartbeat waveform, indicating that the monitoring device 10 does serve as a diagnostic tool for a patient with a heart disease. Figure 14 illustrates a portion of the analog plate 24 of the monitoring device of the present invention. Compared to the analog plate 24 shown in Fig. 5(a), a single-ended output transmitting antenna 21 is used, and the analog plate 24 shown in Fig. 14 uses a differential output transmitting antenna 21*. The monitoring device 1 using the differential output transmitting antenna can greatly increase the bandwidth and greatly increase the waveform amplitude representing the physical activity of the human body. Fig. 15 (a) shows the bandwidth of the monitoring device 1 使用 using the single-ended output transmitting antenna 21. Fig. 15 (b) shows the bandwidth of the monitoring device 1 使用 using the differential output transmitting antenna 2 。. Using the differential output transmit antenna 21, the bandwidth of the monitoring device 10 is about 44.7 megahertz (as shown in Figure 15(b)), while the bandwidth of the monitoring device 1〇 using the single-ended output transmit antenna 21 is only Approximately 44.7 million megahertz (Figure i5(a)

100210

IO607I ΟΟ5366837 -20- 1306023 jin Ding)) The use of the differential output transmitting antenna 21, the monitoring device, the bandwidth can be increased by about seven times. Figure wu) shows the rib artery signal waveform of the monitoring device employed by the single-ended output transmitting antenna 21 and FIG. 16(1) shows the radial artery captured by the device 1Q using the differential output transmitting antenna 21. Signal waveform. Obviously, the amplitude of the radial artery signal waveform shown in Figure (b) is approximately twice the amplitude of the waveform of the sacral iliac artery signal. In other words, the use of the differential output transmitting antenna 21' can increase the representation of the human body. The amplitude of the signal of the physical activity The flexible slot antenna 3 of the present invention is illustrated in Fig. 17. The flexible slot antenna 300 comprises a flexible substrate 3, 2 made of polyamido, and is disposed on a transmitting antenna 31A on the flexible substrate 302 and a receiving antenna 320 identical to the transmitting antenna 31. The flexible substrate 3〇2 allows the flexible slot antenna 3 to be more easily worn on the human body. The transmitting antenna 31A includes a pair of metal blocks 304 and 3048', wherein each of the metal blocks 304 and 3048 has at least one slot 3 12 (for example, a triangular slot provided in a mirror image), and each metal block 3〇4 The lateral width of the feed end 308A of the eight and 304B is smaller than the lateral width of the free end 308B. In addition, the flexible slot antenna 3A further includes a feed end 308A connected to the metal block 304A. Microstrip line 306. Preferably, the metal block 304 A may be a triangle, a fan shape (fan_shapecj) or a T-shape, and the length of the microstrip line 306 is half the wavelength of the ultra-wideband electromagnetic wave. Figure 1 8(a) shows the use of a flexible slot antenna The bandwidth of the monitoring device 1 of 300 is shown, and FIG. 18(b) shows the bandwidth of the monitoring device 1〇 using the flexible antenna 300', V0/100210 1〇6〇71 005366837 -21- 1306023 where the flexible antenna 300 'The slotless transmit antenna 310 having the hard substrate 3〇2' and the receive antenna 320 are as shown in Fig. 17(b). Monitoring using the flexible antenna 300 shown in Fig. 17 (1) The bandwidth of the device is only about 12 mega-megahertz, and the bandwidth of the monitoring device 1 using the flexible slot antenna 3 shown in Fig. 18(a) is still 1 _ 145 MHz. Obviously, the use of flexible substrate 3〇2 and the provision of slots 312 in metal blocks 304A and 304B helps to increase the bandwidth of the monitoring device 1 by a factor of about 10. Figure 19(a) shows the use of a flexible slot antenna. The monitoring device of the 3〇〇 device performs the waveform of the radial artery signal, and FIG. 19(b) shows the waveform of the radial artery signal captured by the monitoring device using the flexible antenna 3〇〇. The amplitude of the radial artery signal waveform of Fig. 19(a) is about four times the amplitude of the waveform of the iliac artery signal of Fig. 19(b). In other words, the flexible substrate 3〇2 is used and the metal block 3〇4a The provision of slots 312 in 304B helps to increase the signal amplitude of the physical activity of the human body. The technical content and technical features of the present invention have been disclosed above, but those skilled in the art can still make based on the teachings and disclosures of the present invention. Various substitutions and modifications may be made without departing from the spirit of the invention. Therefore, the scope of the present invention is not limited by the scope of the invention, and the invention is intended to cover various alternatives and modifications. BRIEF DESCRIPTION OF THE DRAWINGS FIG. 1(a), FIG. 1(b) and FIG. 1(c) illustrate the position of the monitoring device of the present invention at a position where an arterial blood vessel activity can be detected; FIG. 2(a) and FIG. 2(b) illustrates the monitoring device of the present invention; FIG. 30) shows a timing chart of the detected pulse wave; 100210 1〇6〇71 005366837 -22- 1306023 FIG. 3(b) shows a spectrogram of the detected pulse wave of the radiation; A functional block diagram showing the monitoring device of the present invention; FIG. 5(8), FIG. 5(4), and FIG. 5(4) show circuit diagrams of the analog board of the present invention; FIGS. 6(a) and 6(b) show the balanced mixer of the present invention. Figure 7(a) shows the relative relationship between the detected pulse wave received by the balanced mixer and the reference pulse wave; • Figure 7(b) shows the output of the balanced mixer and the first low-pass filter. Figure 10 (a) and Figure 8 (b) compare the timing of the arterial vessels in the resting state and the arteries in the traveling state; Figure 9 shows the balanced mixer of the present invention Spectrum diagram of the output signal; Figure 10 shows the frequency performance of the signal spectrum packet and antenna input to the transmitting antenna of the present invention; Figure 12 (a) shows a loop antenna of the monitoring device of the present invention; Figure 12 (b) shows a bow-tie antenna of the monitoring device of the present invention; Figure 12 (c) shows the present invention The terminal half-wave antenna of the monitoring device; Figure 12 (d) shows the helical antenna of the monitoring device of the present invention; Figure 13 (a) and Figure 13 (b) compare the arterial signal waveform and electrocardiogram captured by the monitoring device of the present invention. Signal waveform; Figure 14 shows a portion of the analog panel of the monitoring device of the present invention; Figure 15 (a) shows the bandwidth of the monitoring device using a single-ended output transmitting antenna; Figure 15 (b) shows the monitoring using a differential output transmitting antenna The bandwidth of the device; 100210 1〇6〇71 005366837 -23- 1306023 Figure 16 (a) shows the waveform of the radial artery signal captured by the monitoring device using the single-ended output transmitting antenna; Figure 16 (b) shows the use of the differential output Fig. 17(a) shows the flexible slot antenna of the present invention; Fig. 17(b) shows the flexible antenna of the present invention; Fig. 18(a) shows flexibility The bandwidth of the slot antenna; Figure 18(b) shows the flexible antenna Wide; FIG i9 (a) a flexible display slot signal waveform of the radial artery fetched antenna of the monitoring device; and FIG. 19 (b) show the signal waveform of the radial artery using fetched flexible antenna of the monitoring device. [Major component symbol description] 2 Clock generator 4 Balanced mixer 5 High-pass filter 6 First low-pass filter 7 First amplifier 8 Second low-pass filter 9 Second amplifier 10 Monitoring device 11 Band 12 Delay line 13 First pulse generator 14 Second pulse generator 15 Analog/digital converter 18 Microcontroller 19 Universal non-synchronous wireless receiver 20 Transmitter 21 Transmitting antenna 21, Transmitting antenna 22 Receiving antenna 23 Antenna board - twenty four-

;:y 100210 106071 0〇5366837 1306023

24 analog board 24' analog board 25 digital board 27 RS232 or USB cable 28 data processing and display unit 30 resistor 31 resistor 32 logic inverter 33 logic inverter 34 capacitor 36 resistor 37 resistor 38 resistor 39 capacitor 40 capacitor 41 capacitor 42 Capacitor 51 Resistor 52 Bypass Capacitor 71 Operational Amplifier 72 Operational Amplifier 73 Operational Amplifier 74 Operational Amplifier 75 Operational Amplifier 76 Connector 77 Electronically Erasable Memory 78 Serial 埠 Driver 79 Adjustable Shunt Regulator 80 Operational Amplifier 102 Logic inverter 103 quartz crystal 104 resistor 105 capacitor 106 capacitor 108 logic inverter 109 logic inverter 220 pull-up resistor 300 flexible slot antenna 300' flexible antenna 302 flexible substrate 302' hard substrate 304A metal block 304B Metal block 306 microstrip line 308A feed end 308 free end 310 transmit antenna 310, slotless transmit antenna

25- 1306023 Receiving Antenna 312 Slot 320 320' Receiving Antenna

•26·

Claims (1)

1306023, X. Patent application scope: 1. A monitoring device for physical activity of a human organ, comprising: a first pulse generator for generating a detection pulse wave; - a transmitting antenna for transmitting the detection pulse wave a human body organ; a receiving antenna 'for receiving a detection pulse wave scattered by the human body; a second pulse wave generator for generating a reference pulse wave; and a balanced mixer comprising: a first input埠 electrically connected to the second pulse generator; # and a second input 埠' electrically connected to the receiving antenna for generating a phase difference signal representing physical activity of the human organ; and a analog/digital conversion The device is configured to convert the phase difference signal into a digital signal. 2. The monitoring device of the physical activity of a human organ according to claim 1, further comprising: φ a clock generator for generating a clock signal; and a delay line electrically connected to the clock generator, wherein the first The pulse wave generator generates the detection pulse wave according to a clock signal of the clock generator, and the second pulse wave generator is electrically connected to the clock generator by the delay line and according to the clock generator The clock signal generates the reference pulse wave. 3. A monitoring device for physical activity of a human organ according to claim 2, wherein the delay line comprises a variable resistor and a capacitor. 4. The monitoring device of the physical activity of a human organ according to claim 1, wherein the hair 1306023 comprises: a high pass filter electrically connected to the balanced mixer; a first low pass filter electrically connected to the high pass filter a first amplifier electrically coupled to the first low pass filter; a second low pass filter electrically coupled to the first amplifier; and a second amplifier electrically coupled to the second low pass filter . 14. A monitoring device for physical activity of a human organ according to claim 13, wherein the first amplifier is an instrumentation amplifier. 15. A monitoring device for physical activity of a human organ according to claim 13, wherein the second low pass filter is a fourth order active Battens filter. 16. The monitoring device of the physical activity of a human organ according to claim 1, wherein the analog/digital converter is embedded in a microcontroller. 17. A monitoring device for physical activity of a human organ according to claim 16, further comprising a transceiver electrically coupled to the microcontroller, the data being transmitted to a display element by a universal serial bus. 18. The monitoring device of physical activity of a human organ according to claim 16, further comprising a communication connection cable 2 electrically connected to the microcontroller to transmit data to the display element. ^ 19. A monitoring device for the physical activity of a human organ, comprising: a transmitting antenna for transmitting - detecting a pulse wave to a human body, wherein the transmitting antenna comprises - a pair of metal blocks, each metal block having less - slot 'The system is mirrored; a receiving antenna wave; and an analog signal processing unit for receiving the detecting pulse scattered by the human organ, comprising: 100210 1〇6〇71 005366837 -29- 1306023 a first input port, electrical Connected to a reference pulse generator; and a second input port electrically connected to the receiving antenna to generate a signal representative of physical activity of the human body. 20. The monitoring device of the physical activity of a human organ according to claim 19, wherein the transmitting antenna and the receiving antenna are disposed on a substrate composed of polyamidomine. 21. A monitoring device for physical activity of a human organ according to claim 19, wherein the width of the feed end of each of the metal blocks is less than the width of a free end. 22. A monitoring device for physical activity of a human organ according to claim 19, wherein each of the metal blocks is triangular, fan-shaped or T-shaped. 23. A monitoring device for physical activity of a human organ according to claim 19, wherein the slot is triangular. 24. A monitoring device for physical activity of a human organ according to claim 19, further comprising a microstrip line coupled to one of the feed ends of the metal block. 25. A monitoring device for physical activity of a human organ according to claim 19, wherein the receiving antenna is identical to the transmitting antenna. 26. A method of extracting physical activity of a human organ, comprising the steps of: transmitting an ultra-wideband electromagnetic wave to a human organ; measuring a phase difference signal between the detected pulse wave scattered by the human organ and a reference pulse wave And generating a signal representative of the physical activity of the human organ based on the phase difference signal. 27. The method of extracting the physical activity of a human organ according to claim 26, which measures the phase difference signal according to the following equation: = ^ Ad = VTa 100210 IO6O7I ΟΟ5366837 -30- 1306023 where / indicates the frequency of the detected pulse wave, c indicates the speed of light, £ indicates the relative dielectric constant of the skin tissue of the human body, and r indicates the movement of the physical movement of the human organ toward the direction of the detected pulse wave. Speed, 7; indicates the time when the human organ moves by a predetermined distance Δί/. 100210 106071 005366837 -31-