TWI361059B - Pulsed ultra-wideband sensor and the method thereof - Google Patents

Description

1^105,9 VI. Description of the invention: [Technical field to which the invention pertains] The present invention relates to a medical instrument for testing human physiological parameters, in particular, using radar assistance to diagnose a human body in static or (four) Medical dynamic state of physiological parameters [Prior Art] The measurement device using ultra-wideband radar can solve many problems that cannot be solved by traditional quantities. For example, the 韶 聚 聚 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超 超The patient has a salty mat. φ Ma ~ This wood is a chance, and the ultra-wideband sensor does not require special laboratories or specially trained operators. ·, : Broadband sensors provide a non-contact diagnostic method that cannot be achieved by large-scale burns or traditional diagnostic methods for skin diseases. By using a kind of sensor, patients can diagnose and save diagnosis without undressing. ^Between the use of An Wang, the ultra-wideband sensor also has low energy and light radiation.

Sex. Compared to X-ray tomography, the amount of light emitted by ultra-wideband sensors is reduced by several orders of magnitude. In addition, when using the ultra-wideband sensor as a medical measuring instrument, it is not necessary to use the measuring instrument as a whole-discovery, ancient master, and 毋', and there is no need to use a disposable component or a consumer profile to maintain the diagnostic technology. The required cost can also be significantly reduced by 0 according to the current classification of 7 (see I.Ya.Immoreev on November, 1998 in Journal 〇f Bauman's MGTU series Instrument making^ ^^.^Ultra_wideb^d radars : new possibilities , unique problems, the feature of system or I.Ya.immoreev, November 2, 2002, in Applied electronics, Kharkov Vol. 1, pp. 122-140, The possibilities and features of ultra-wideband radio systems, An ultra-wideband radar system is a radar that satisfies the following signal bandwidth conditions: 〇.25<(fupper-U/(fupper+fUwer)<1 ' where fupper and flower are the lower bounds of the signal bandwidth, respectively. The frequency bandwidth (fupper-f丨.wer) of the wide-band radar should be greater than 5〇〇ΜΗζ (see the First Report and Or of the EF Docket 98-153 of the Federal Communications Commission FCC on April 22, 2002). Der). As the distance resolution of ultra-wideband radar increases, the content of the messages it sends increases. The circuit design of various well-known pulsed ultra-wideband sensors is used to monitor the respiratory and cardiovascular systems of patients. A pulsed ultra-wideband sensor is disclosed, for example, in US Patent No. 5,519,400 (issued May 21, 1996), which utilizes phase c〇de modulation to control the movement of the object under test. The transmitting antenna uses a short-time pulse as a reference signal and an excitation signal. The device has a signal transmission k, and the signal transmitting end has a transmitting antenna, and transmits an ultra-wideband signal with a frequency of 2 GHz to 10 GHz. a delay block, which generates a control signal to determine a time delay between the pulses. The device has a receiving end having a receiving antenna that receives a discrete signal according to a trigger signal (gating signa) of the time delay block Pulse signal. The trigger signal delays the reception time of a transmission signal, wherein the delay time is equal to the transmission signal line. The analyte and the reflection of the time required to receive antenna. The delay time is determined by the distance of 1361059 between the sensor and the object to be tested. The time delay block provides a delay between the detection of the pulse signal and a reception of the pulse signal. The pulse signals are modulated by the time delay block. The modulated signal is encoded to avoid interference from adjacent radar sensors. The signal receiving end includes a sync block and two orthogonal channels, wherein the sync block is used to synchronize the signal receiving end and a modulated signal. The normal channel is used to process a reflected signal, wherein one channel and one reference signal operate in the same phase, and the other channel and the reference signal have a phase difference of 90 degrees. The output data of these channels is used for subsequent analysis. The channels are converted according to a high speed controllable switching mechanism when receiving a reflected signal, and each channel has a filter and a signal amplifier. In the function of the conventional radar sensor, the signals of the orthogonal channels cannot be processed at the same time, and the reflected electromagnetic signals must be processed in the single channel switching mode, so that the orthogonal signals can not be processed simultaneously to reduce the signal mode. The signal is distorted. • Since the signals of the orthogonal channels cannot be processed simultaneously during the measurement process, the sensor cannot obtain accurate physiological parameters of the analyte at a certain distance. The specific distance between the object to be tested and the sensor is the area of the so-called Wind Zone, in which the phase sensitivity of the sensor is obtained even if the sensor receives a large amplitude reflection detection signal. Still drastically falling. The number of such dead zones and their spacing depends on the distance between the object to be tested and the sensor and the length of the pulse within the probe signal. The presence of such dead zones and the limited measurement distance (which depends on the pulse length of the detection signal) result in a decrease in the measurement accuracy of the patient's physiological parameters at a particular measurement distance, thus limiting such pulses The practical application of ultra-wideband sensors. The sensor can only be used in a state where the patient is completely unable to move and the patient and the sensor are at a fixed distance, and any change in the patient's position needs to be readjusted at the sensor end. In this case, the position of the sensor relative to the object to be tested needs to be adjusted to avoid the situation where the patient is in the blind spot. An automatic distance tracking system automatically adjusts the distance of the sensor's. However, it not only makes the design of the instrument more complicated, but also does not guarantee that the object to be tested is in the blind zone when the expensive automatic distance tracking system is applied. . U.S. Patent Publication No. 2004/0249258 (published on Dec. 9, 2004) discloses another ultra-wideband sensor to monitor physiological parameters of a patient. The device is a low power pulsed ultra-wideband radar comprising a transmit and receive antenna. The device uses a short-time pulse as a reference detection signal. The apparatus includes a fixed frequency pulse generator, a transmitter, a receiver, a delay signal generating block, an analog to digital signal converter, a signal processing block, a data display block, and a control and sync block. The signal processing block processes the reflected signals in a statistical manner. The receiver enhances the reflected signal energy by stepwise amplification, and converts the reflected signal into a digital signal by the analog to digital signal converter. However, when the characteristics of the sensor are included in some spatial regions, the amount of data of the reflected signal is reduced, and the sensor cannot simultaneously generate reliable physiological parameters for the patient's organs. U.S. Patent No. 5,573,012 (issued on Nov. 12, 1996) discloses 1 361 059 A pulsed radar apparatus for monitoring various physiological parameters, including the physiological parameters of the patient's heart vasculature and respiratory organs. The operation of the instrument is based on a reflected signal from the object under test and an average voltage signal that produces a signal for modulating an audio generator. The device includes a signal converter for converting the measured voltage of the reflected signal to a modulated amplitude to the frequency audio signal. The device further includes a pulse generator and an accumulator. The pulse generator is operative to generate a pulse that turns on an input circuit of a signal receiver. The accumulator is used to accumulate the signal of the receiver input circuit. The receiving signal of the device can be processed by chopping and amplifying to control various parameters. However, the signal processing circuit of the device cannot eliminate the dead zone between the object to be tested and the sensor. In addition, the sensor is not an ultra-wideband sensor. One of the sensors drives the generator at a frequency of 1 MHz and a signal bandwidth of no more than 0.1 MHz. The sensor measures and processes the reflected signal by the Doppler effect. Therefore, the sensor cannot provide a signal containing sufficient data as an ultra-wideband sensor. The prior art which is closest to the present invention is U.S. Patent No. 4,085,740 (issued Apr. 25, 1978), which discloses a pulsed radar sensor for monitoring physiological parameters of the cardiovascular system and respiratory organs of a patient. The sensor includes a generator that generates an oscillating electromagnetic wave having a frequency of 10 GHz. The generated electromagnetic wave is modulated by a modulation block and sent to the object to be tested via a transmitting antenna of the transmitter. The detection signal reflected by the object to be tested is received by the receiving antenna of a receiver, and Input to the two channels of the input circuit of the receiver. At the same time, a reference probe signal is also sent to an attenuator, wherein the attenuator is also

i'S -10· 1361059 The mixer receives the same phase and contains two channels. The reference signal of one of the first channels of the receiver. Another reference signal is passed through a phase shifting circuit to produce a phase difference of 9 degrees, and the output of the phase shifting circuit is coupled to a second input of a mixer of the second channel of the receiver. The receiving end of the sensor has two channels for processing the reflected signal, wherein each channel has a -mixer, and the output of the mixers is connected in series to a detector to demodulate the reflected signal, and the signal is again It is processed via a signal amplifier and a wave. When monitoring the physiological parameters of the patient, the mixers of the channels output signals of the sinusoidal waveform. When demodulating a composite signal comprising two phase shifted sinusoids, the amplitude is defined by the angular velocity of the two signals (four) of the input to the mixer. The amplitude of the relative phase difference between the two channels by the signal and the amplifier of the signal processing channel is the frequency of the movement or heartbeat of the patient's chest. The first channel of the receiving end is used to separate the signal representing the frequency of movement of the chest, and the second channel is used to separate the signal representing the heartbeat frequency. The two births are defined by amplifiers and filters that are adjusted based on the relative amplitude and frequency of the patient's physiological parameters.

It is necessary to fix the amount of data of the sensor when the object to be tested and the sensor are separated (that is, the dead zone). The application of this sensor is limited by the distance. Even if the object to be tested is only slightly moved from -11 to 1361059, the sensor cannot be used. The signal processing mode of the above-described sensor of the prior art utilizes a correlation system to process the reflected signal. The operation of the system is based on multiplying a detection signal and a delayed reflection signal, wherein the delay time is the time of the signal transmitted from the transmitting end to the object to be tested and then reflected back to the receiving end. Commonly used detection signals utilize short-term pulses with a duration that does not exceed one oscillation period. The output signal of the correlation system for processing the reflected signal is proportional to the phase difference between the reflected signal and the detected signal.

When the object to be tested is stationary, the amplitude Z of the processed output signal is determined by the following correlation formula: Ζ = ^ψ-ηΤ0ο〇8(φ) > (1) where the maximum amplitude of the 探测 detection signal , the maximum amplitude of the 丨 反射 reflection signal; 最大 the maximum amplitude of the 探测 detection signal, the total number of oscillating waves in the η detection signal. The phase difference in equation (1) is determined by the time when the electromagnetic wave travels back and forth to the object to be tested and the sensor: φ = ω0^^- = 4π— (2) C λ where % = 2 the circumference of the private detection signal Frequency; f 〇 is the average frequency of the spectrum of the signal; C is the electromagnetic wave transmission speed; λ is the wavelength of the oscillating wave inside the signal;

Ri is the distance between the analyte and the sensor. FIG. 1 shows a graph z(Ri)t〇 normalized by the amplitude of the output signal obtained by the correlation system according to the distance of the object to be measured. As shown in the figure, there are many blind spots in the working distance between the sensor and the object to be tested, and the output signal of the sensor approaches zero in the blind areas. The existence of such dead zones is independent of the reflectivity (effective reflection area) of the object to be tested. The distance between the boundaries of the blind areas is proportional to λ/4 = TqC/4, which is determined by the period of the oscillating wave of the detection signal. The number N of the blind zones is inversely proportional to the period τ 震 of the oscillating wave of the probe signal or the wavelength 探测 of the probe signal. The lower the period (the higher the frequency), the greater the number of dead zones within the measurement working distance. In particular, if the working distance is 2 meters and the average frequency of the probe signal spectrum is 6 GHz, there will be about 16 blind zones, and the boundary distance of the blind zones is approximately equal to 12.5 mm. Therefore, it is highly probable that the chest surface of the patient to reflect the detection signal is located within the blind zone when measuring the heartbeat and respiratory rate. In case the object to be tested is located in the blind zone and its amplitude of movement is less than one quarter of the wavelength of the oscillating wave in the detection signal, it will be quite difficult to measure the movement of the object to be tested. These conditions will have an adverse effect on the accuracy of the measurement results, which is an unacceptable result for the diagnosis of the patient. When the amplitude of the object to be tested repeatedly moves, for example, the deep breathing of the patient, and the average frequency of the spectrum of the detection signal is high, the waveform of the output signal of the correlation system is compared with the actual description of the movement of the object to be tested. There is a distortion of the degree of correlation. Therefore, it is difficult to achieve high accuracy in the heartbeat and respiratory rate of patients determined by such conditions. The amplitude z(t) of the output signal of the correlation processing system can be expressed by the following publication: 13- {"S3 1361059: Z (〇=心 cos_ + burning), (3) where &=-^«7; The maximum energy value of the reflected signal and the detection signal interact with each other, and output to a load of one unit impedance; burning = 2 call = if j is based on the phase difference between the object to be tested and the distance between the sensors; rush) = 2% ^^ =知¥厂仰) is the instantaneous phase according to the movement of the object to be tested

Value; F(Qt) is the movement rule of the object to be tested; Ω = 2 π f is the frequency of the repetitive motion of the object to be tested; t is the current time; Δ R is the maximum displacement of the object to be tested. Assuming that the distance of the object to be tested is Ri from the sensor and the object to be tested moves according to the simple harmonic motion and has a circumferential frequency Ω and an amplitude AR, the formula (3) can be adjusted to the following form:

Z(t) = Em cos^4^-^^sin(Qi) + ^π~ (4). Figures 2 through 9 show waveform diagrams of the output signals of the correlation system (change the amplitude 输出(1) of the output signal and the spectrum 2(6) of the amplitude and frequency). The change of the amplitude Ζ(1) corresponds to only the -variation in the figure, and each graph corresponds to a different variable m (m is equal to 〇.5 in Fig. 2 and Fig. 3, and Fig. 4 and Fig. 5^ are equal to 2, Fig. 6 And in Figure 7, m is equal to 5, and Figure 8 and Figure 9*m are equal to 1〇), such as! ' ' λ. Figure 2 to Figure 9 show the change of the maximum position of the object to be tested. The displacement 1 Δ R and the corresponding variable m correspond to the change of the output signal. The oscillating frequency measured by the object to be tested is 14 Hz. 1361059 is 1 Hz. The f丨 is the frequency of the reflected signal. As shown in the figure, the waveform of the output signal is different from the actual displacement of the object to be tested, wherein the maximum displacement of the object to be tested is ΔR, and the wavelength of the detection signal is again. When a single channel signal processing circuit is applied, if Δκ > λ (m is 2, 5, and 10 as shown in Figs. 4 to 9, respectively), the function of the amplitude and moving speed of the object to be tested will be difficult to determine. If the maximum displacement Δ R of the object to be tested is smaller than the wavelength of the detection signal (ΔΙΙ < λ ), the output signal of the orthogonal channel will contain both variables and constant components. It is worth noting that the constant component of the reflected signal has useful information for each stationary object, and the object to be tested is also among the stationary objects. Under the % know-how device, the constant component is removed by the filters in each channel when processing the reflected signal. Therefore, such useful information that can accurately determine physiological parameters will be lost. In order to obtain the information of the movement of the object to be tested, a special stylized signal calibration can be performed on the stationary object to be tested, wherein the information exists in the constant component of the reflected signal. If the position of the object to be tested changes, the signal calibration step should be repeated. However, this also results in lengthy measurement time and complex software design. SUMMARY OF THE INVENTION The present invention simultaneously processes the reflected signal from the object to be tested in two channels, and separates the reflected signal carrying the largest message content for subsequent processing and determines the heartbeat frequency, respiratory rate or other physiological parameters of the patient with accuracy. By the solution of the present invention, it is possible to achieve an increase in sensor phase sensitivity and an accurate determination of the heartbeat frequency, the frequency of breathing, or the frequency of other physiological parameters when the patient moves within the working range. This effect is provided by a pulsed ultra-wideband sensor. The sensor comprises a control unit, a detection signal forming path, a transmitting antenna, a receiving antenna, a detecting signal transmitting path, a reflected signal receiving path and a phase shifting circuit. The control unit is used to form a time delay in pulse synchronization. The probe signal forming path includes a coherent pulse sine wave generator coupled to the control unit. The output of the probe signal transmission path is connected to the transmitting antenna. The reflected signal receiving path includes two orthogonal channels to process a reflected signal. Each channel contains a signal mixer. A first input of the signal mixer is coupled to the receive antenna. An input of the phase shift circuit is coupled to an output of the probe signal forming path. The output of the phase shifting circuit is coupled to the first input of the signal mixer of the second channel. A sensor in accordance with an embodiment of the present invention includes a first electronic switch and a ~hop and respiratory frequency calculation path. The heartbeat and respiratory frequency calculation path includes two filters, two adders, two signal amplitude calculation blocks, two signal energy calculation blocks, two integrators, two comparators, two signal acquisition blocks, and two Reference signal generation block, a second electronic switch first electronic switch, a heartbeat frequency calculation block and a respiratory frequency calculation block. The input end of the first electronic switch is connected to the output end of the detection signal forming path, and the first output end of the first electronic switch is connected to the input end of the detection signal transmission path. The second output of the first electronic switch is connected to the second input of the signal mixer of the first channel and the wheel of the phase offset electrical m -16 - path. The cmth early element. The control wheel of the sub-switch is connected to the wheel of the second and second filters. The first input of the first adder to the first and the -* ii .3⁄4 . ^ , is connected to the second input of the first -^.. TM de-asserted state and connected to the output of the first / wave filter end. The first input of the second additive-alpha method is connected to the output of the channel of the brother. The second input of the second method is connected to the output of the filter. . . The first input terminal of the first signal multiplication block is connected to the first-addition output terminal. The second input terminal of the multiplication block is connected to the output end of the first reference signal generating block. The first input of the second signal multiplication block is coupled to the output of the second adder. The second input end of the second signal multiplication block is connected to the output end of the second reference signal generation block. The input of the first integrator is coupled to the output of the first signal multiplication block. The output of the first integrator is connected to the first wheel end of the second electronic switch and the input end of the first signal energy calculation block. The input of the second integrator is coupled to the output of the second signal multiplication block. The output of the second integrator is coupled to the second input of the second electronic switch and the input of the second signal energy calculation block. An output of the first signal energy calculation block is coupled to the first input of the first comparator. The output of the second signal energy calculation block is coupled to the second input of the first comparator. An output of the first comparator is coupled to a control input of the second electronic switch. • ί Si -17- 1361059 The input of the first signal amplitude S ten block is connected to the output of the first filter. The round output end of the first signal amplitude calculation block is connected to the first input end of the second comparator. The input of the second signal amplitude calculation block is connected to the output of the second filter. An output of the second signal amplitude calculation block is coupled to a second input of the second comparator. An output of the second comparator is coupled to a control input of the third electronic switch. A first input of the third electronic switch is coupled to an output of the first filter. A second input of the third electronic switch is coupled to the output of the second filter. An output of the third electronic switch is coupled to an input of the respiratory frequency calculation block. An output of the first electronic switch is coupled to an input of the heartbeat frequency calculation block. The method for measuring a physiological parameter according to an embodiment of the present invention includes: first, having a first physiological parameter and a second physiological parameter, a first message signal and a second message signal to generate only the first physiological parameter a first _ chopping signal and a second filtering signal; adding the first message signal and the first filtering signal to generate a first addition signal having only one of the second physiological parameters; adding the second message The signal and the second filtered signal are used to generate a second addition signal having only one of the second physiological parameters; performing a correlation calculation between the first added signal and a first reference signal to generate a first correlation signal; Performing a correlation calculation between the second addition signal and a second reference signal to generate a first correlation signal, according to the amplitude of the first data signal and the second filter wave signal from the first filtered signal and Selecting a first physiological parameter signal from the second filtered signal; and extracting, according to the first correlation signal and the second correlation signal, the first correlation signal and the second correlation -18-1361059 signal in A second physiological parameter signal is selected. The present invention is exemplified by a specific embodiment of a pulse type ultra-wideband sensor for measuring a heartbeat frequency, a respiratory frequency or other physiological parameters. [Embodiment] As shown in FIG. 10, the pulse type ultra-wideband sense The detector comprises a control unit 1 and a detection signal forming path. The control unit i is used to form a delayed sync pulse signal. The probe signal forming path includes an externally excited microwave generator 2 as a coherent pulse sine wave generator. The pulsed ultra-wideband sensor further includes a transmitting antenna 3, a receiving antenna 4, a detecting signal transmitting path, a first electronic switch 5 and a reflected signal receiving path. The reflected signal receiving path includes two channels for processing the reflected signal. The probe signal forming path includes a buffer amplifier 6 and a band pass filter 7, wherein the buffer amplifier 6 and the band pass filter 7 are connected in series to the microwave generator 2. The band pass filter 7 is connected to the input end of the first electronic switch 5. The detection signal transmission path includes a band pass filter 8 and an amplifier 9', wherein the band pass data device 8 and the amplifier 9 are connected in series to the transmitting antenna 3, and an input terminal of the amplifier 9 is connected to the first electron The first output of switch 5. The reflected signal receiving path includes a band pass filter 1 and a low noise amplifier 11, wherein the band pass filter 10 and the low noise amplifier 11 are connected in series to the receiving antenna 4, and the low noise amplifier 11 The output is connected to the two parallel channels for processing the reflected signal. The reflected signal receiving path further includes a phase shift circuit 12. The first i S] 19- 1361059 channel for processing the reflected signal comprises a signal mixer 13 having an output system and a band pass filter 14, a low frequency amplifier 15, a low frequency filter 16 and an analog to digital position. The converters 17 are connected in series. The first input of the signal mixer 13 is connected to the output of the low noise amplifier 11, and the second input of the signal mixer 13 is connected to the second output of the first electronic switch 5. The second channel for processing the reflected signal comprises a signal mixer 18, the output of which is connected in series with a bandpass filter 丨9, a low frequency amplifier 2〇, a low frequency filter 21 and an analog to digital converter 22. connection. The first input end of the signal mixer 18 is connected to the output of the low noise amplifier ,, and the second input end of the signal mixer 18 is connected to the first via the phase shift circuit i 2 The second output of the electronic switch 5, wherein the phase shifting circuit 12 is configured to provide a phase difference of a detection signal of 9 degrees. The lower frequency limits of the low frequency filters 16 and 21 are about 〇1 Hz to select a signal whose frequency band is higher than the cutoff frequency. The control unit 1 is configured to form a delayed sync pulse signal. The display diagram is not shown in FIG. 9, and includes a driver generator 23, a transmitter sync and probe signal control path, and a receiver sync path. The transmitter synchronization path includes a first short pulse generating unit 24 for generating a short pulse sync signal. The receiver synchronization path includes a controllable digital delay line 25 and a second short pulse generation unit %' constituting a first output $ of the control unit 1, wherein the first@out terminal is connected to the first electronic switch 5 Control input. The transmit and receive sync paths are both connected to the input terminal of the OR gate circuit 27, wherein the output of the OR gate circuit 27 is the second output terminal of the control unit 1 and the second output terminal is connected to the microwave generator : The control input. A schematic diagram of the heartbeat and respiratory rate calculation path is shown in Figures 12 and 13, and includes two filters 28 and 29, two adders 30 and 31, two signal amplitude calculation blocks 32 and 33, and two signal energy calculations. Blocks 34 and 35, two integrators 36 and 37, two comparators 38 and 39, two signal multiplication blocks 40 and 41, two reference signal generation blocks 42 and 43, a second electronic switch 44, and a third The electronic switch 45, a respiratory rate calculation block 46, a heartbeat frequency calculation block 47, and a data display block 48. The filters 28 and 29 are used to select the signal of the chest vibration and the heartbeat signal at the frequency of the input signal. The signals are included in the reflected signal, wherein the reflected signal is a composite waveform of the heartbeat and respiratory function of the patient. The bands 28 and 29 with bandpass effects provide smoothing of portions of the reflected signal that have heartbeat frequency characteristics. This waveform contains the frequency characteristics of heartbeat and chest vibrations. The upper cutoff frequencies of these filters 28 and 29 are approximately 1 Hz. An input of the first chopper 28 is coupled to an output of the first channel for processing the reflected signal. An input of the second filter 29 is coupled to an output of the second channel for processing the reflected signal. In the present embodiment, the inputs of the filters 28 and 29 are connected to the analog outputs to the outputs of the digital converters 17 and 22, respectively. . The first input of the first adder 30 is coupled to the output terminal of the first channel for processing the reflected signal, wherein the analog to digital converter (4) is the output of the first channel. The first adder is as a second input terminal; the output of the wave filter 28. The first 1361059 input of the second adder η is coupled to the output of the second channel for processing the reflected signal, wherein the analog to digital converter 22 serves as the output of the second channel. The second input of the second adder 31 is coupled to the output 0 of the second filter 29. The first input of the first signal multiplication block 40 is coupled to the output of the first adder 30. The second input of the first signal multiplication block 40 is coupled to the output of the first reference signal generating block 42. The first input of the second signal multiplication block 41 is coupled to the output of the second adder 31. The second input of the second signal multiplication block 41 is coupled to the output of the second reference signal generating block 43. The input of the first integrator 36 is coupled to the output of the first signal multiplication block 4A. The output of the first integrator 36 is coupled to the first input of the second electronic switch 44 and the input of the first signal energy calculation block 34. The input of the second integrator 37 is coupled to the output of the second signal multiplication block 41. The output of the second integrator 37 is coupled to the second input of the second electronic switch 44 and the input of the second signal energy calculation block 35. The output of the first signal energy calculation block 34 is coupled to the first input of the first comparator 38. The output of the second signal energy calculation block 35 is connected to the second input of the first comparator 38. The wheeled end of the first comparator 38 is coupled to the control input of the second electronic switch 44. An input of the first signal amplitude calculation block 32 is coupled to an output of the first filter 28. The output of the first signal amplitude calculation block 32 is coupled to the first input of the second comparator 39. The second signal amplitude calculation -22- 1361059 is input to the output of the second filter 29. The output of the second signal amplitude calculation block 33 is coupled to the second input of the second comparator 39. The output of the second comparator 39 is coupled to the control input of the third electronic switch 42. - a first input of the third electronic switch 45 is connected to the output of the first filter 28. A second input of the third electronic switch 45 is coupled to the output of the second filter 29. The output of the third electronic switch 45 is coupled to the input of the beer frequency calculation block 46. The output of the second electronic switch 44 is connected to the input of the heartbeat frequency calculation block 47. The data display block 48 has a first input coupled to the output of the heartbeat frequency calculation block 47. The second input of the data display block 48 is coupled to the output of the respiratory frequency calculation block 46. In an aspect of the embodiment, as shown in FIG. 12, the input ends of the first reference signal generating block 42 and the second reference signal generating block 43 are respectively connected to the outputs of the adders 30 and 31. . The output signals of the adders 3 and 31 are used to form a reference signal, which is an instantaneous reflection signal for a period of time. The length of the reference signal is selected to be 3 seconds, and the reference signal is passed to the signal multiplication blocks 4A and 41. In another aspect of the embodiment, as shown in FIG. 13, the first reference signal generating block 42 and the second reference signal generating block 43 are used to generate a fixed-shaped reference signal. The reference signal is stored to the reference signal generating blocks 42 and 43 and transmitted to the inputs of the equal sign multiplication blocks 4A and 41. The length of the reference signal can be selected as 3 seconds, and the waveform can be defined by the following formula: -23- iS] 1361059 m ι)> exp It is worth noting that the phase sensitivity can be improved as long as the circuit of the present invention can be implemented. And detecting the effect of moving the object to be tested, many of the components and blocks used in the embodiments of the present invention can be omitted. In particular, in some cases, the data display block can be omitted. In the detection signal transmission path, the transmitting antenna 3 can be directly connected to the first output end of the first electronic switch 5.

Further, in some embodiments of the present invention, the transmitting antenna 3 and the receiving antenna 4 may be integrated into one single block of a transceiver (not shown). The block may be coupled to different components during different periods of the transceiver, such as coupled to the probe signal transmission path when the transmit antenna is in operation, or coupled to the reflected signal receive path during operation of the receive antenna, wherein the transceiver Then alternately acts as a radio wave transmitter and a radio wave receiver. The transmit and receive paths can be alternately coupled to the transmit and receive antennas via an additional electronic switch. The application of the single block allows the two independently operated antennas to be integrated into a single component within the sensor. The operation of the pulse type ultra-wideband sensor described above is as follows. The drive generator 23 generates a sync pulse signal whose period is τ 〇 and 敎 is chopped (the timing chart of the sync pulse signal can be seen in Fig. 14). Then, the pulse signals are respectively received by two paths: that is, the transmitter synchronization path and the receiver synchronization path. In the transmission H-synchronization path, the first burst signal is generated by the first short pulse generated by the rising edge of the j-th sync pulse signal, and the delay signal is delayed by td as shown in FIG. The time interval of the short pulse signal is determined by the root loss -24- [S3 1361059 required time interval of the detection signal. In the receiver synchronization path, the synchronization pulse signal is delayed by the delay time td2 by the controllable digital delay line 25, as shown in FIG. 15, wherein the delay time k is a detection signal transmitted to the object to be tested and then reflected back. The time required for the detector. The delay time tda defines the working distance between the object to be tested and the sensor, and can be expressed by the following equation: the center is the distance between the object to be tested and the sensor, and c is the speed of the wave. The short pulse signal having a delay time of td3=tdl is generated by the second short pulse generating unit 26' on the rising edge of the second group of synchronous pulse waves, as shown in FIG. The formed short pulse signal is transmitted to the first output of the control unit 1, wherein the first output terminal is connected to the control input of the first electronic switch 5. The control unit 1 combines the synchronization signals formed on the synchronization paths into a single synchronization signal by the OR gate circuit 27, which is a periodic pair of short pulse signals, as shown in FIG. The time interval between the pair of short pulse signals is t d 2 〇 The period τ 〇 of the pair of pulse signals is set by the drive generator 23. The synchronization signals including a pair of pulse signals are transmitted to the second output of the control unit 1, wherein the second output is connected to the control input of the microwave generator 2. When the microwave generator 2 receives the synchronization signal, two adjacent homologous pulse chords of interval h are generated, as shown in FIG. The pair of coherent pulse chops generated by the microwave generator 2 are transmitted to the input terminal of the first electronic switch 5 via the buffer amplifier 6 and the band pass filter 7. The first electronic switch 5 is controlled by a signal output by the first output of the control unit 1. The first electronic switch 5 controls the detection signal -25- to form a switching of the path signals, that is, the detection signals are transmitted to the detection signal transmission path or the reflected signal receiving path. In the initial state, the switching of the first electronic switch 5 is as shown in Fig. 10. The first coherent pulse wave generated by the microwave generator 2 enters the detection signal transmission path. The amplifier 9 amplifies the detection signal to compensate for the energy loss caused by the band pass filter 7 and the band pass filter 8. The band pass filters 7, 8 and 10 are combined to pass a frequency band of 3 GHz to 10 GHz to suppress signal igniting outside the band. The detection signal is transmitted via the transmitting antenna 3 and transmitted to the object to be tested. After the elapse of td2, the detection signal is reflected back to the sensor via the object to be tested, and the receiver synchronization path also generates a short pulse synchronization signal, wherein the synchronization signal is transmitted to the first output terminal of the control unit 1 to The control input of the first electronic switch 5. When the control unit 1 receives the short pulse synchronization signal, the control unit 1 switches its switch. Therefore, the detection signal forming path is connected to the second input terminals of the signal mixers 13 and 18. The reference detection signal is transmitted to the signal mixer 18 after the phase shift circuit 12 provides a phase difference of 90 degrees. Accordingly, the second coherent pulse sine wave generated by the microwave generator 2 enters the second channel for processing the reflected signal with a phase difference. The phase and the homologous pulsed chord with a phase difference serve as reference signals for the number of mixers 13 and 18. The signal reflected by the object to be tested is received by the receiving antenna 4 and passes through the band pass filter 10 and the low noise amplifier U, wherein the band pass filter 10 is used to reduce external electromagnetic waves. Noise. The filter and the signal after the 1361059 are transmitted to the channels for processing the reflected signals, that is, the signal mixers 13 and 18 as the phase detectors. After correlating with the reference detection signals transmitted to the second input terminals of the signal mixers 13 and 18, the channels for processing the reflected signals generate two signals: one is located in the first channel The phase signal and another signal having a phase difference of 90 degrees in the second channel. In these channels, the signals are separated by the bandpass filters 14 and 19, respectively, and the low frequency amplifiers 15 and 2 are amplified. The low frequency filters 16 and 21 select the signals by frequency and separate the signals by the cutoff frequency as the lower limit, wherein the cutoff frequency is about 01 Hz, which corresponds to the lower limit of the sucking frequency. The separated and amplified signals are digitized by the analog to digital converters 17 and 22. As shown in Fig. 20, a signal god +) is formed at the output end of the first channel where the signal and the reference probe signal are in phase. As shown in Fig. 22, 'another signal Ζζ(ί) = Sin(p(i)+i?i) is formed at the output end of the second channel, wherein the signal and the reference detection signal have a phase difference of 9 degrees . The signals are transmitted to the heartbeat and respiratory rate calculation path, as shown in Figures 12 and 13. The signal of the first channel is transmitted to the first filter 28, and the signal of the second channel is transmitted to the first filter 29. The filters have an upper cutoff frequency of 1 Hz' to attenuate the components of the signal with high frequency heartbeats. Therefore, the output signals of the filters 28 and 29 are signals separating the components representing the patient's breathing from the reflected signals of the patient's chest vibrations and heartbeat components. • 27-iS] 1361059 After the selection of the frequency, the output signals of the filters 28 and 29 enter the second wheel of the adders 30 and 31, the input of the third electronic switch 45, and The first signal amplitude calculation block 32 and the input end of the second signal amplitude meter block 33. The signals of the first channel and the second channel are transmitted to the first inputs of the adders 30 and 31.

The adders 30 and 31 are used to separate their turn-in signals. The adders 30 and 31 are signals that include the patient's chest vibration and heartbeat components to eliminate the respiratory component of the patient' to form a signal containing only the patient's heartbeat component at the output. The discrete signals after frequency selection and characterization of physiological parameters (heartbeat and respiration) are used for subsequent correlation processing.

The signal multiplication blocks 40 and 41 and the integrators 36 and 37 are consuming to the output of the above-mentioned block as a correlation system for processing such heartbeat-only component signals. The reference signals output by the reference signal generation blocks 42 and 43 are transmitted to the second input terminals of the signal multiplication blocks 4A and 41. As shown in Figure 12, in an architecture of the present embodiment, the inputs of the reference signal generating blocks 42 and 43 are coupled to the outputs of the adders 3A and 31. In this architecture, a fixed length of the processed signals is taken as a reference signal. The length of the signal is selected to be at least equal to the average period of the reflected signal. In this architecture, the signal length is chosen to be 3 seconds. The reference signal generation blocks 42 and 43 store the output signals of the adders 30 and 31 to a memory unit for a specific time, for example, 60 seconds. These signals are used as reference signals and transmitted to the signals

[SI 28· 1361059 The second input of blocks 40 and 41 until the next storage action. As shown in FIG. 13, in another architecture of the embodiment, the reference signal generating blocks 42 and 43 are used to generate a fixed waveform reference signal. The reference signals of the predetermined waveforms are stored in the memory cells of the reference signal generating blocks 42 and 43, and are continuously transmitted to the input terminals of the signal multiplication blocks 4A and 41. In this architecture, the reference signal of the fixed length and the fixed waveform may be defined by the following formula: D = + _1) xex < - ge The length of the signal is selected to be at least equal to the average period of the reflected signal oscillation. In this architecture, the signal length is chosen to be 3 seconds. The reference signals are transmitted by the multiplication operations of the signal multiplication blocks 4 and 41 and the output signals of the blocks 4G and 41 of the m-counter are transmitted to the integrators 36 such as the points ||36 and 371 and The 37 performs the integral action of the input signals at each time. Fig. 21 and Fig. 23 are timing charts showing the output signals Ζι(1) and Z2(1) of the integral points H 36 and 37, respectively. It can be seen from the timing diagrams of the output signals Ζι(1) and &(1) shown in FIG. 21 and FIG. 23 that the signal of the first channel outputted through the correlation system has a periodicity, and the frequency of the hop is determined according to the signal. Signals with higher accuracy H-channels are more diffuse, and their periodicity is less obvious, and the heartbeat frequency determined by this signal is difficult to obtain the desired accuracy. The output signals of the integrators 36 and 37 are transmitted to the second electronic open: 4: input and the input of the first signal energy calculation block 34 and the second signal ': leaf nose block 35. The signal heart (1) enters the input end of the second electronic switch 44 and the input end of the tenth arithmetic block 34 from the first input end of the second electronic switch 44 and the first signal. The signal Z2(1) enters the second input of the second electronic switch 44 and the input of the second signal energy calculation block 35 from the output of the integrator 37. To select a signal that can be used to more accurately determine the heartbeat frequency, the signal can be selected based on the energy of the signal. The signal energy calculation blocks 34 and 35 are used to calculate the energy of the first and second channel signals. The signal energy calculation blocks 34 and 35 calculate the sum of the squares of the signal amplitudes over a fixed period of time. In this embodiment, the sum of the squares of the amplitudes of the signals is calculated in a fixed time. The operation of the signal energy calculation blocks 34 and 35 is performed after each measurement, and is instantaneously moved along the input signal by a sliding window (the length of which is 3 seconds) to perform an operation. The signal energy calculation blocks 34 and 35 respectively transmit their calculation results to the first and second inputs of the first comparator 38. The first comparator 38 selects a signal having a larger energy. Figure 24 shows a comparison of the calculated signal energies E(t) » The upper half of the comparison graph e(1) shows the output of the first signal energy calculation block 34. The lower half of the comparison map e(1) shows the output of the second signal energy calculation block 35. It can be seen from Fig. 24 that the signal energy of the first channel substantially exceeds the signal of the second channel. According to the comparison result, the first comparator 38 transmits a control signal to the control input of the first electronic switch 44, wherein the control signal is used to switch the second electronic switch 44. The switching result of the second electronic switch 44 should conform to the signal selected to have a larger energy. The output signal of the first integrator 36 is switched to the heartbeat frequency calculation block 47 for subsequent operations. 1361059 • The heartbeat frequency calculation block 47 is “looking for the local maximum of its input signal and its time point. The heartbeat frequency of the patient can be calculated based on the time point found. The data display block 48 is transmitted by the signal of the heartbeat frequency that is not calculated.

For selection - a signal that can be used to more accurately determine the respiratory rate, the signal can be selected based on the amplitude of the signal. Because of the low frequency characteristics of the patient's chest vibration, this embodiment compares the amplitudes of the output signals of the wavers 28 and 29. The respiratory rate is generally about an order of magnitude less than the heart rate. Therefore, the decisive factor in selecting the respiratory signal is whether the maximum amplitude of the signal is clearly available. The amplitude of the first channel signal is greater than the amplitude of the second channel signal by the timing diagrams of Z丨(1) and Z2(1). As shown in Figures 2() and 22, the flat signal value of the first channel signal is approximately the location, and the average relative peak value of the second channel signal is approximately 3 units.

The signal amplitude calculation blocks 32 and 33 are used to calculate the correlation of the respiratory signals separated by the choppers 28 and 29. The first signal amplitude calculation block 32 outputs a signal indicating the amplitude of the first channel signal. The second signal amplitude calculation block 3 3 outputs a signal indicating the amplitude of the second channel signal. The signals for indicating the amplitude of the first channel signal and the amplitude of the second channel signal are respectively transmitted to the first and second inputs of the second comparator 39. The second comparator 39 is used to compare the output signals of the amplitude calculation blocks 32 and 33. Based on the comparison, the second comparator 39 transmits a control signal to the control input of the third electronic switch 45. The switching result of the third electronic switch 45 should conform to the selected signal having a large amplitude. In the case of the actual -31 - 1361059%, the output signal of 'the first - Yi Yi 28 is switched to the calculation of the call (4). (4) Frequency The beer frequency calculation block 46 is used to find the input signal. The local maximum and its time point. The respiratory rate of the patient can be calculated based on the time point found. The signal indicating the calculated respiratory frequency is transmitted to the data display block 48. The data is displayed in block 48. The measurement results of the heartbeat and respiratory rate are displayed in a convenient form, in particular, presented on the screen in a manner. Figure 25 is a processing circuit in accordance with an embodiment of the present invention. The processing circuit 2500 is applied to a A pulsed ultra-wideband sensor, such as a pulsed ultra-wideband sensor according to an embodiment of the invention, is used to measure heartbeat and respiratory rate. The processing circuit 2500 includes a first filter 2501, a second filter 2502, and a The first signal amplitude calculation unit 2503, a second signal amplitude calculation unit 2504, a first electronic switch 2505, a first adder 25〇6, a first adder 2507, and a first signal integration list 25〇8, a second signal integration unit 2509, a first signal energy calculation unit 2510, a second signal energy calculation unit 2511 and a second electronic switch 2512. The first filter 2501 is configured to receive an in-phase signal. For example, the analog signal is analogous to the output signal of the digital converter 17. The second filter 2502 is configured to receive an orthogonal signal, such as an analog signal to the output signal of the digital converter 22. The first signal amplitude calculating unit 2503 is configured to calculate the output signal. The amplitude of the output signal of the first filter 250 i. The second signal amplitude calculation unit 2504 is configured to calculate an amplitude of the output signal of the second filter 2502. The first electronic switch 25〇5 is used according to the first The signal amplitude calculation unit 2503 and the second signal-32-1361059 amplitude calculation unit 2504 output the output signal of the first filter 2501 or the second filter 2502. The first adder 2506 is configured to perform the first A subtraction operation is performed between the output signal of the filter 2501 and the input signal. The second adder 2507 is configured to perform a subtraction operation between the output signal and the input signal of the second filter 2502. The first signal integration unit 2508 is configured to calculate a correlation score between the output signal of the first adder 2506 and a first reference signal. The second signal integration unit 2509 is configured to calculate an output signal of the second adder 2507 and a The correlation energy of the second reference signal is calculated by the first signal energy calculation unit 2510 for calculating the energy of the input signal of the first signal integration unit 2508. The second signal energy calculation unit 2511 is configured to calculate the second signal integration unit. The energy of the input signal of 2509. The second electronic switch 2512 is configured to output the first signal integration unit 2508 or the second signal integral according to the calculation result of the first signal energy calculation unit 2510 and the second energy amplitude calculation unit 2511. The output signal of unit 2509. In some embodiments of the present invention, the first signal integration unit 2508 includes a first signal multiplication block 2515 and a first integrator 2516. The first signal multiplication block 25 15 is used to calculate the product of the round-trip signal of the first adder 2506 and the first reference signal. The first integrator 2516 is configured to calculate an integrated value of the output signal of the first signal multiplication block 2515. In another embodiment of the present invention, the second signal integration unit 2509 includes a second signal multiplication block 2517 and a second integrator 2518. The second signal multiplication block 25 17 is used to calculate the product of the output signal of the second adder 2507 and the second reference signal. The second integrator 2518 is configured to calculate an integrated value of the output signal of the second signal multiplication block 2517. In the embodiment of the present invention [S] - 33 - 1361059, the processing circuit 2500 further includes a first comparator 2513 and a first comparator 2514. The first comparator 2513 is configured to compare the calculation results of the first signal amplitude calculation unit 2503 and the second signal amplitude calculation unit 25〇4 to control the first electronic switch 25〇5. The second comparator 2514 is configured to compare the calculation results of the first signal energy calculating unit 251 〇 and the second signal energy calculating unit 2511 to control the second electronic switch 2512. In some embodiments of the present invention, the first reference signal and the second reference signal are a fixed waveform. In another embodiment of the present invention, the first reference signal is generated according to the input signal of the first adder 25〇6, and the second reference signal is generated according to the input signal of the second adder 2507. Produced. In some embodiments of the present invention, the processing circuit 25 further includes a first reference signal generating block for generating the first reference signal, and a second reference signal for generating the second reference signal. Square. The sensor implemented in accordance with the present invention can sequentially select the frequency of the reflected signal in two channels, and can separate the signal indicating the breathing from the signal indicating the heartbeat, and can perform the correlation operation of the separated signals, respectively. A signal with a large amount of data is selected for each physiological parameter to be measured to accurately perform subsequent heartbeat and respiratory frequency calculations. However, the physiological parameters measured by the sensor and method according to the present invention are not limited to the heartbeat frequency and the respiratory frequency, but can be applied to physiological parameters such as intestinal peristalsis. By calculating the heartbeat and respiratory frequency by the above-mentioned processing of the reflected signal and the channel of the specific structure, the sensitivity of the sensor phase sensitivity and the measurement accuracy of the physiological parameters can be greatly improved. In addition, by eliminating the influence of the blind spot in the working distance on the measurement result, the parameter for measuring the moving object to be tested also becomes available. 34- m 1361059 Row 0 The pulsed ultra-wideband sensor of the present invention can be applied to Medical equipment to monitor the cardiovascular system and respiratory organs with high accuracy under static or inactive conditions. The technical and technical features of the present invention have been disclosed as above, and those skilled in the art can still make various substitutions and modifications without departing from the spirit and scope 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 Figure 1 shows a graph Z(Ri)T〇 normalized according to the relative distance Ri of the static object to be tested and the amplitude of the output signal of one of the correlation processing systems; Figure 2 shows that m is equal to 〇, 5 o'clock, the output signal Z(t) of a correlation processing system; Figure 3 shows the amplitude frequency spectrum Z of the output signal of a correlation processing system when m is equal to 0 5 (f〇; Figure 4 shows at m When equal to 2, the output signal Z(t) of a correlation processing system; Figure 5 shows the amplitude frequency spectrum Z of the output signal of a correlation processing system when m is equal to 2 (f〇; Figure 6 shows that m is equal to 5 When the output signal of the correlation processing system is Z(t); Figure 7 shows that when m is equal to 5, the output signal of the correlation processing system is 35- 1361059. The amplitude frequency spectrum z (f〇; Figure 8 shows When m is equal to 10, the rotation signal Z(t) of a correlation processing system; 'Figure 9 shows the amplitude frequency spectrum ζ(ι) of the output signal of a correlation processing system when m is equal to 10; Figure 1〇 a schematic diagram of a probe signal forming path, a probe signal transmission path, and a reflected signal receiving path; 11 shows a schematic diagram of a control unit; FIG. 2 shows a schematic diagram of a heartbeat and respiratory frequency calculation path according to the first embodiment of the present invention; FIG. 13 shows a schematic diagram of a heartbeat and respiratory frequency calculation path according to the second embodiment of the present invention. ; shows the timing diagram of the synchronous pulse wave u(1) of the output signal of the drive generator; FIG. 15 shows the timing diagram of the synchronous pulse wave U(1) of the output signal of a controllable digital delay line; FIG. 16 shows the output of a first short pulse generating unit. Timing diagram of the sync pulse wave (1) of the signal; Figure 17 shows a timing diagram of the sync pulse wave U(t) of the output signal of the first short pulse generating unit; The timing diagram of the synchronous pulse wave u(1) of the output signal of the control unit; Fig. 19 shows the timing diagram of the homologous pulse chord U(1) of the output signal of the wave making Is, and the -36 - 1361059: display - the first Channel + chopper wheel signal z, (1) 夂 output signal Zi (t) Figure 21 shows a timing diagram of a first integrator of a first channel; Figure 22 shows a timing diagram of one of the second channels;The first filter's turn-off signal Z2(t) Figure 23 shows a timing diagram of one of the second channels 篦 _ ^ the first integrator output signal Z2(t);

FIG. 24 shows a comparison diagram E(t) of output signals of a first (upper half curve) and a second (lower half curve) signal energy calculation block; and FIG. 25 shows a processing circuit according to an embodiment of the present invention. . [Main component symbol description]

1 control unit 2 microwave generator 3 transmitting antenna 4 receiving antenna 5 first electronic switch 6 buffer amplifier 7 bandpass filter 8 bandpass filter 9 amplifier 10 bandpass filter 11 low frequency amplifier 12 phase offset circuit i S] - 37- 1361059

13 Signal mixer 14 Bandpass filter 15 Low frequency amplifier 16 Low frequency filter 17 Analog to digital converter 18 Signal mixer 19 Bandpass filter 20 Low frequency amplifier 21 Low frequency filter, Boyi 22 Analog to digital converter 23 Drive Generator 24 first short pulse generating unit 25 controllable digital delay line 26 second short pulse generating unit 27 or gate circuit 28 first filter, waver 29 second wave benefit 30 first adder 31 second adder 32 A signal amplitude calculation block 33 Second signal amplitude calculation block 34 First signal energy calculation block 35 Second signal energy calculation block 36 First integrator 37 Second integrator i'Si -38 - 1361059 38 First comparator 39 Second comparator 40 first signal multiplication block 41 second signal multiplication block 42 first reference signal generation block 43 second reference signal generation block 44 second electronic switch 45 third electronic switch

46 Respiratory Frequency Calculation Block 47 Heartbeat Frequency Calculation Block 48 Data Display Block 2501 First Filter 2502 Second Filter 2503 First Signal Amplitude Calculation Unit 2504 Second Signal Amplitude Calculation Unit 2505 First Electronic Switch

2506 first adder 2507 second adder 2508 first signal integration unit 2509 second signal integration unit 2510 first signal energy calculation unit 2511 second signal energy calculation unit 2512 second electronic switch 2513 first comparator 2514 second comparison -39- 1361059 2515 First Signal Multiplication Block 2516 First Integrator 2517 Second Signal Multiplication Block 2518 Second Integrator

Claims (1)

VII. Patent application scope: 1. A pulse type ultra-wideband sensor for measuring heart rate and respiratory frequency, wherein the pulse type ultra-wideband sensor comprises a control unit, a detection signal forming path and a transmitting antenna a receiving antenna, a detecting signal transmitting path, a reflected signal receiving path and a phase shifting circuit, wherein the control unit is configured to form a delayed synchronous pulse wave, the detecting signal forming path comprising a homology connected to the control unit a pulse sine wave generator, the output end of the detection signal transmission path is connected to the transmitting antenna, and the reflected signal receiving path includes two first and second channels for processing the reflected signal, wherein each channel & has a signal a mixer having a first input coupled to the receiving antenna. The input of one of the phase shifting circuits is coupled to an output of the probe signal forming path, and an output of the phase shifting circuit is coupled to the second channel a second input end of the signal mixer for processing a reflected signal, the pulsed ultra-wideband sensor further comprising: a first electron Off; and a heartbeat and respiratory frequency calculation path, including two filters, two adders, two signal amplitude calculation blocks, two signal energy calculation blocks, two integrators, two comparators, two signal multiplication blocks Two reference signal generating blocks, a second electronic switch, a third electronic switch, a respiratory frequency calculation block and a heartbeat frequency calculation block; wherein the input end of the first electronic switch is connected to the detection signal forming path The first output end of the first electronic switch is connected to the input end of the detection signal transmission path, and the second output end of the first electronic switch is connected to the second input of the signal mixer of the first channel And the input end of the phase shift circuit, the controller terminal of the first electronic switch is connected to the control unit, and the wheel ends of the first and second filters are respectively connected to the output end of the second channel To process-reflect the m number, the first input of the first adder is coupled to the output of the first channel to process a reflected signal, the first: adder of the first adder The human terminal is connected to the output end of the first wave state and the first input of the second adder is connected to the output of the second channel to process a reflected signal, and the second input of the second adder is connected To the output of the second filter, the first input end of the first signal multiplication block is connected to the output end of the first adder, and the second input end of the first signal multiplication block is connected to the first reference signal Generating an output end of the block, the first input end of the second signal multiplication block is connected to the output end of the second adder, and the second input end of the second signal multiplication block is connected to the output of the second reference signal generation block The input end of the first integrator is connected to the output end of the first signal multiplication block, and the output end of the first integrator is connected to the first input end of the second electronic switch and the first signal energy calculation block. The input end of the second integrator is connected to the output end of the second signal multiplication block, and the output end of the second integrator is connected to the second input end of the first electronic switch and the second signal An input end of the energy calculation block, the output end of the first signal energy calculation block is connected to the first input end of the first comparator, and the output end of the second signal energy calculation block is connected to the first comparator a second input end, the first comparative output is connected to the control input end of the second electronic switch, and the input end of the first signal amplitude calculation block is connected to the first output of the first filter An output end of the amplitude calculation block is connected to the first input end of the second comparator, and an input end of the second signal amplitude calculation block is connected to an output end of the second filter, and an output end of the second signal amplitude calculation block Connected to the second input end of the second comparator, the round output end of the second comparator is connected to the control input end of the third electronic switch, and the first input end of the third electronic switch is connected to the first wave The output end of the third electronic switch is connected to the output end of the second filter, and the output end of the third electronic switch is connected to the respiratory frequency calculation block At the input end, the output of the second electronic switch is connected to the input end of the heartbeat frequency meter. 2. The pulsed ultra-wideband sensor of claim 1, further comprising a data display block, wherein the first input of the data display block is connected to the output end of the heartbeat frequency meter block and the data display block One of the second inputs is coupled to the output of the respiratory frequency calculation block. 3. The pulsed ultra-wideband sensor of claim 1, wherein the input of the first reference signal generating block is connected to the output of the first adder, and the input of the first reference signal generating block is connected to The output of the second adder. 4. The pulsed ultra-wideband sensor of claim 1, wherein the reference reference generation blocks are used to generate a reference signal for the fixed waveform. 5. The pulsed ultra-wideband sensor of claim 1, wherein the probe signal forming path comprises a buffer amplifier and a band pass filter, wherein the buffer amplifier and the band pass wave wave are connected in series to the same-called pulse sine wave a generator, and an output of the band pass filter is coupled to an input of the first electronic switch. 6. The pulsed ultra-wideband sensor according to claim 1, wherein the wheel-out end of each signal mixer is connected to the heartbeat and respiratory frequency calculation via a series bandpass filter, a low frequency amplifier and a low frequency filter. path. The pulsed ultra-wideband sensor of claim 1, wherein the reflected signal receiving path comprises a band pass filter and a signal amplifier, wherein the band pass filter and the signal amplifier are connected in series to the receiving antenna, and the signal amplifier The output is switched to the channel for processing the reflected signal. The pulsed ultra-wideband sensor of claim 1, wherein the detection signal transmission path comprises a band pass filter and a signal amplifier, wherein the band pass filter and the signal amplifier are connected in series to the transmit antenna, and the signal amplifier The input end is connected to the first output end of the first electronic switch. A pulse type ultra-wideband sensor according to claim 1, wherein the control unit comprises a drive generator and a transmitter synchronization path and a receiver synchronization path and a gate circuit connected in parallel to the drive generator, wherein The transmitter synchronization path includes a first short pulse generating unit, the receiver synchronization path includes a controllable digital delay line and a second short pulse generating unit, and the output end of the second short pulse generating unit is the control unit An output terminal, the first output end of the control unit is connected to the control input end of the first electronic switch. The input end of the gate circuit is connected to the output end of the transmitter synchronization path and the output end of the receiver synchronization path. The output end of the OR gate circuit is a second output end of the control unit, and the second output end of the control unit is connected to an input end of the coherent pulse wave generator. A pulse type ultra-wideband sensor comprising a processing circuit, the processing circuit comprising: a first filter 'waveper for receiving an in-phase signal; 1361059 a second filter 'for receiving an orthogonal signal; a first signal amplitude calculation unit 'for calculating an amplitude of an output signal of the first wave filter; a second signal amplitude calculation unit 'for calculating an amplitude of an output signal of the second chopper; a first electronic switch, Outputting an output signal of the first chopper or the second filter according to a calculation result of the first signal amplitude calculation unit and the second signal amplitude calculation unit; a first adder for performing the first a subtraction operation between the output signal of the filter and the input signal; a second adder for performing a subtraction operation between the output signal of the second filter and the input signal; a first signal integration unit for calculating the first a correlation signal of an adder and a first reference signal; a second signal integrating unit for calculating an output signal of the second adder and a second parameter a correlation signal of the test signal; a first signal energy calculation unit for calculating the energy of the input signal of the first signal integration unit; and a second signal energy calculation unit for calculating the wheel entry of the second signal integration unit An energy of the signal; and a second electronic switch for outputting the round signal of the first signal integration unit or the second signal integration unit according to the calculation result of the first signal energy calculation unit and the second energy amplitude calculation unit . 11. The pulsed ultra-wideband sensor of claim 10, wherein the first reference, [S] 45 1361059 is a fixed waveform. 12. The pulsed ultra-wideband sensor of claim 10, wherein the first reference signal is generated based on an input signal of the first adder. 13. The pulsed ultra-wideband sensor of claim 10, wherein the second reference signal is a fixed waveform. 14. The pulsed ultra-wideband sensor of claim 1, wherein the second reference signal is generated based on an input signal of the second adder. 15. The pulsed ultra-wideband sensor of claim 10, wherein the first signal integration unit comprises: a first interrogation multiplication block 'for calculating an output signal of the first adder and the first reference signal a product; and a first integrator 'for counting the integral value of the output signal of the first signal multiplication block. 16. The pulsed ultra-wideband sensor of claim 10, wherein the second signal integration unit comprises: a first signal multiplication block 'for calculating a product of the output signal of the second adder and the second reference signal And a first integrator for counting the integral value of the output signal of the second signal multiplication block. 17. The pulsed ultra-wideband sensor according to the e-come 10, wherein the processing circuit further comprises a first comparator for comparing the calculation of the first signal amplitude calculation unit and the second signal amplitude calculation unit The result is to control the first electronic switch. 1 . The pulsed ultra-wideband sensor according to claim 1 , wherein the processing circuit includes a second comparator for comparing the first signal energy calculation unit and the second signal The calculation result of the energy calculation unit controls the second electronic switch. 19. The pulsed ultra-wideband sensor of claim 10, wherein the processing circuit further comprises a first reference signal generation block to generate the first reference signal. 2. The pulsed ultra-wideband sensor of claim 10, wherein the processing circuit further comprises a second reference signal generating block to generate the second reference signal. 21* — A method for measuring a physiological parameter, comprising: filtering a first message signal and a second message signal having a first physiological parameter and a second physiological parameter to generate only one of the first physiological parameters a filtered signal and a second chopping signal; adding the first message signal and the first filtered signal to generate a first addition signal having only one of the second physiological parameters; adding the second message signal and the a second filtering signal to generate a second addition signal having only one of the second physiological parameters; performing correlation calculation between the first addition signal and a first reference signal to generate a first correlation signal; The correlation between the two-phase signal and the second reference signal is calculated to generate a second correlation signal; and the amplitudes of the first filtered signal and the second filtered signal are from the first filtered signal and the second filtered signal Selecting a first physiological parameter signal; and 47 1361059, according to the first correlation signal and the second correlation signal~ running amount from the first correlation signal and the second correlation information Select - _ first signal processing parameter. 22. The method of claim 21, wherein the first message signal and the 笫_-message signal have a phase difference of 90 degrees. 23. The method of claim 21, wherein the correlation calculation of the first summation signal and the first spring signal is accomplished by integrating a product of the first addition signal and the first reference signal. The method of claim 21, wherein the correlation calculation of the first addition signal and the second reference signal is performed by integrating a product of the second addition signal and the second reference signal. 25. The method of claim 21, further comprising: determining the first physiological parameter based on a local maximum of the first physiological parameter signal. 26. The method of claim 21, further comprising: determining the second biometric parameter based on a local maximum of the second physiological parameter signal. 27. The method of claim 21, wherein the first physiological parameter is a respiratory frequency. 0 28. The method of claim 21, wherein the second physiological parameter is a heartbeat frequency. 48