TW201206397A - Pulse detector - Google Patents

Abstract

The present invention relates to a pulse detector. The pulse detector comprises a light source, a light sensor and a sensing circuit. The light source is configured on a skin tissue of a living body, and generates at least a first light to irradiate on the skin tissue, and the first light will form a first light by reflection of the skin tissue; the light sensor is configured on the skin tissue, and there is an interval between the light sensor and the light source, and the light sensor received the second light; and, the sensing circuit is connected with the light sensor, and correspondingly generates a sensing signal according to the second light received by the light sensor, and the sensing signal is corresponded to a pulse variation of the living body; in which, the interval is corresponded to a wavelength or brightness of the first light and the second light. Thus, the present invention may be used for realtime preliminary pulse determination, and the detector according to the present invention is simple and more convenient than the ordinary pulse detector.

Description

201206397 VI. Description of the Invention: [Technical Field] [0001] The present invention relates to a light sensing device, and more particularly to a pulse sensing device that senses a pulse using a method of detecting reflected light. [Prior Art] [0002] ❹ ❹ Pulsation sensing technology is a non-invasive optical metrology technique for detecting changes in blood volume in vascular beds in tissues. Generally, both transmissive and reflective types of sensing probes are used. Use different light sources in combination with light sensors to manipulate blood pulsation physiological signals. In the mechanism design of the penetrating pulsation sensor, the light source and the sensor are respectively at the two ends of the tested tissue, and the body part that can be transmitted through the light must be selected for detection. Usually, the sensing probe is used to detect the penetrating finger, ear, or nose, etc., and the light source also needs to select a light wavelength that has a strong penetrating ability as a light source. The reflective probe design is designed to place the light source and sensor on the same side and can be detected at any part of the body. It must be designed to take into account the optical properties of the tissue to be tested. The appropriate source wavelength and appropriate power are chosen to detect the pulsation signal that enters the tissue and is reflected back from the tissue. 099126534 Non-invasive reflective probes are easier to fix, so they are easier to use for long-term detection, and the measurement site is not limited to areas where the body can penetrate light, such as the forehead, so it does not affect hand activity. Because the scattered light detected by the reflective probe is usually a short distance and the light is absorbed less, the lower light source power can be used and the safety is improved. As published in 2001 by Dr. Cai Zhenglun and others in the paper "Simulation and Measurement of Light Distribution in Biological Tissues", the distribution of light in tissues and the fine path (4) reveals that the use is not page 3 / A total of 30 pages of the form number A0101 - only < 九 0992046543-0 201206397 The application of the source of the test, such as the "Pulse-wave measuring apparatus" of US Patent No. US 57661 31 and the US Patent No. US 5906582 The "Organism information measuring method and arm wear type pu1se-wave measuring method" discloses a light source using a blue light 450 nm and a green light 505 nm as a reflection type pulsation sensor. Furthermore, Mendelson, Yitzhak, and Burt D. Ochs, "Non-invasive Pulse Oximetry Utilizing Skin Reflectance Photop1ethysmography, M IEEE Transactions on Bioffiedieal Engineering, vol. 35, pp. 798-805, 1988. j, Mendelson The person uses red light and near-infrared light as the light source for sensing, and the distance between the sensor and the light source R is measured at a distance of 4 to 11 mm, and the brightness of the surface reflected light of the skin tissue is measured, and the pulsed alternating current signal is analyzed. Changes with DC signals. Another example is "Reuss, James L., and Daniel Siker, "The pulse in reflectance pulse oximetry:

Modeling and experimental studies, M Journal ·

Clinical Monitoring and Computing, vol. 18' no. 4, pp. 289-299, 2004", which discloses the use of Monte Carlo optical simulation to analyze the distance between the source and the photosensor from 1 mm to 17 mm. In the case, the reflectance of the red light of a wavelength of 660 nm and the near-infrared light of a wavelength nanometer are irradiated to a plurality of layers of skin tissue (such as a dermis tissue, a dermal tissue, and a subcutaneous tissue). In the above-mentioned sensing method and sensing device, when the total perfusion flow of the living body changes with the physiological changes of the living body, the low-frequency signal of the measurement result greatly changes, so it is easy to cause the pulse sensing station 099126534 Form No. A0101 Page 4 / Total 30 Page 0992046543-0 201206397 The situation of saturation distortion caused by the associated sensing signal. Conversely, when the distance between the light source and the light sensor is large, the light penetrates the path longer, so the light is in the living body. The amount of blood in the inside is also relatively large, and the measurement of the living body is weakened by the light scattering, so that the signal is small, so the signal is relatively poor, but the amount of blood in the path is also large. Therefore, both the high frequency perfusion index and the low frequency perfusion index increase. The resulting measurement of the pulsation is distorted and loses its detection accuracy. In view of the above problems, the present invention provides a pulse sensing device,

G It uses the distance between the light sensor and the light source to control the wavelength or brightness of the light to avoid the influence of the first path scattering of the light in the skin tissue, and avoid the accuracy and stability of the pulse sensing device. SUMMARY OF THE INVENTION [0003] The main object of the present invention is to provide a tactile sensing device that uses a pitch to control the wavelength or brightness of light used for detection to achieve better accuracy of pulse sensing. And stability. A secondary object of the present invention is to provide a pulse sensing device that is further integrated with an integrated circuit using a pulse sensing device to allow the pulse sensing device to be applied to pulse sensing at various locations. The invention provides a pulse sensing device, comprising: a light source, a light sensing and sensing circuit. The light source and the money detector are disposed on a skin tissue of a living body, and the light sensor has a distance between the light source and the light source. Further, the sensing circuit is connected to the light sensing H. The light source generates at least a first light to be irradiated to the skin tissue, the first light is reflected by the skin tissue to form a second light, so that the light sensor receives the first light' and the sensing circuit is connected The photo sensor correspondingly generates the __sensing signal according to the second light received by the light sensing unit 099126534

The form number is deleted 1 ^ 5 30 I 0992046543-0 201206397 , and the sensing signal corresponds to the pulse of the living body. Furthermore, the distance between the rotation of the pulse sensing device of the present invention and the barrier is associated with the wavelength or brightness of the first level and the second light, and thus the present invention can control the first by the spacing. Light and the wavelength or brightness of the second light. 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 。 Referring to the first A and first beta diagrams, which are block diagrams of a pulse sensing device in accordance with a preferred embodiment of the present invention. As shown in the figure, the present invention is a pulse sensing device 1 that includes a sensing module 2, a ten control processing circuit 14, a display unit ι6, and a power source 18, wherein the sensing module 12 includes a The light source 122, a light sensor 124 and a sensing circuit 126. The light source 12 2 and the light sensor 12 4 are disposed on a skin tissue 32 of a living body 3 ′ and the sensing circuit 126 is connected to a light sensor 124 , the light source 12 22 and the light sensor 124 . Between the true food and the distance R, which is the linear path distance of the light path emitted by the light source 12 2 to the light sensor 1 24, and further, as the pitch R changes, the light source 122 is spaced. When the R is shorter, the measured brightness is stronger, and when the distance R is longer, the measured brightness is weaker, but the electronic noise amplitude of the photosensor 124 itself is fixed. Therefore, the signal noise ratio obtained by the photo sensor 124 when receiving the low-light second light 224 is also poor. The light source 122 generates at least a first light ray 222 and is irradiated to the skin tissue 32. The first light ray 222 is reflected by the skin tissue 32 to form a second light ray 224, that is, the skin tissue 32 includes an epithelial tissue 322, a form. No. 101 0101 0992046543-0 Page 6 of 30 201206397 - dermis tissue 324 and a sub-level woven 326, the light sensor 124 receives the second light ray 224, the sensing circuit 126 is based on the light sensor 124 The second light ray 224 is received to generate a sensing signal corresponding to a pulse change of the living body 30, that is, a volume change of blood of at least one blood vessel in the skin tissue 32 is associated with the second light 324. The change in brightness or the change in wavelength, wherein the pitch R is associated with the wavelength or brightness of the second light ray 224 received by the light sensor 124. Referring to the first diagram, the pulse sensing device 1 further includes a circuit base .. . . . . .

The board 20 and a fixing member 22' are disposed on the circuit board 2, the sensing module 12, the control processing circuit 14, the display unit 16, and the power source 18. The fixing member 22 is used to fix the pulse sensing device. On the skin tissue 32, the fastener 22 of the present invention can be a 绷k stretch or a sticker or a bandage. The control processing circuit 14 is connected to the sensing circuit 126 and receives the sensing signal generated by the sensing circuit 126. The control processing circuit 14 generates an output according to the sensing signal generated by the sensing circuit 126. a signal, and the output signal corresponds to the pulse change. The display unit 126 displays an output image according to the output signal. The power source 18 generates a plurality of power signals and transmits them to the sensing module 12, the control processing circuit 14 and the display unit 16' to supply power. Please refer to the second A diagram and the second B diagram together, which is a schematic structural diagram of another preferred embodiment of the present invention. As shown, the pulse sensing device 10 of the present invention is integrated into a small circuit. As shown in FIG. 2A, the light source 122 of the sensing module 12, the light sensor 124, and the sensing circuit 126 of the sensing module 12 are disposed on one surface of the circuit substrate 20. The device 124 is disposed in the sensing circuit 126 ′ and the light source 122 is a light emitting diode. 099126534 Form No. A0101 Page 7 / Total 30 Page 0992046543-0 201206397 The sensing circuit 126 is an integrated circuit (Integrated ,, Ic). As shown in FIG. 2B, the control processing circuit 14 and the display unit 16 are disposed on the other side of the circuit board 2, and the control processing circuit 14 is also an integrated circuit. In this embodiment, the display unit 16 is also In addition to the LED, the display unit 16 can also be a liquid crystal display or a seven-segment display. The power supply i 8 is a thin battery embedded in the circuit board 20. Further, the present invention can integrate the measurement circuit (3) and the control processing circuit 14 into an integrated circuit. The spacing R ranges from 2 mm to 8 mm. The first light 222 generated by the light source 122 has a wavelength ranging from 40 nanometers to 11 nanometers, and the spectrum of the preferred embodiment of the light source 122 in the present invention is blue light (463 nm ± 25 nm). , green light (543 nm ± 5 〇 nanometer), yellow green light (571 nanometer soil 25 nm), and red light (634 nm ± 15 nm). The larger the blood absorption coefficient corresponding to the wavelength of the light source, the greater the ability of the light representing the wavelength to be absorbed by the blood. The larger the scattering coefficient of the skin corresponding to the wavelength of the light source, the greater the degree of scattering when the light advances, and the smaller the ability of the wavelength of light to penetrate the skin tissue, the shallower the light can reach. Among the above four light sources, 463 nm blue light penetrates into the skin/Zhudu about 0.2 mm, 543 nm green light penetrates into the skin to a depth of about 0.4 mm, and 571 nm yellow-green light penetrates into the depth of the skin. 5 mm, while the red light 634 nm penetrates into the skin to a depth of about 毫米62 mm. The depth of the above penetration only represents the intensity of the light decaying to a depth of 37% of the incident light. In fact, the light can still enter deeper. Part. In addition, in the light sources of the above four wavelengths, the reflected brightness obtained by scattering is weakened as the pitch R increases, and the attenuation of the red light is significantly flatter than the sorrow of the other three colors. Therefore, the light source 12 2 For red light, the spacing r can be 099126534. Form number A0101 Page 8 / Total 30 pages 0992046543-0 201206397 Up to 8 mm, and when the light source 122 is yellow-green or green or blue, the spacing R can be as far as 4 to 5 Millimeter. The first light ray 222 is gradually absorbed by the skin tissue 32 from the shallow to the deep in the skin tissue 32, and after being reflected by the dermis layer 324 of the skin tissue 32, forms a second light ray 224, and the surface of the skin tissue 32 reflects light instantaneously. The dynamic balance is achieved, and the brightness of the light is stable and does not change. This part is the DC signal (DC) in the sensing signal. As shown in the third figure, the AC signal of the sensing signal contains the high frequency pulsation. Signal (achi(;h) and low frequency variation signal, and as shown in the upper left corner of the enlarged waveform diagram, wherein the high frequency pulsation signal is a waveform with a frequency varying from 0. 5 Hz to 4 Hz, and the low frequency pulsation signal is at a frequency a smoother waveform below 0.5 Hz, and when the local arterial vasoconstriction or vein is squeezed, affecting blood flow and changing the flow of blood, that is, the volume of blood in the blood vessel is affected by the change of blood vessel contraction, resulting in The relative change of the optical signal in the skin tissue is to form a low frequency pulsation signal, that is, the amplitude change of the low frequency pulsation signal is associated with blood in the blood vessel. The change in volume. When the heart contracts every time, the blood in the blood vessel is pressed and pushed toward the wall, thus forming a pulsation of the blood vessel, which relatively affects the change of the optical signal, that is, the formation of a high-frequency pulsation signal, that is, The amplitude change of the high frequency pulsation signal is related to the volume change of the blood in the blood vessel. The perfusion index is a percentage value of the pulsating alternating current signal and the pulsating direct current signal, and the pulsating alternating current signal can be further divided into a low frequency variation signal of 0. 5 Hz or less and 0. 5 to 4 Hz high frequency pulsation signal. Thus, the amplitude change of at least one alternating current signal included in the sensing signal is related to the volume change of blood in the blood vessel. As shown in the fourth figure, the low frequency blood volume changes The brightness change 099126534 Form No. A0101 Page 9 / Total 30 Page 0992046543-0 201206397 The proportional relationship with DC brightness can be expressed by the low frequency perfusion index pi, which uses the value of the low frequency perfusion index to determine the quantity of the frequency change signal The magnitude of the drift, and when the spacing is 3 mm to 5 mm, the low frequency perfusion index is greater than 5%. It defines the percentage of the pulsating DC signal and the signal lines such as low perfusion index below 05,) as shown in Equation 1. ΡΙι=^^χ100« — -----___ ( 1 ) Moreover, the far-frequency perfusion index PI1 increases with the distance! ^, the higher the low-frequency perfusion index 卩^, that is, the AC pulsation signal changes the duck degree The greater the proportion of DC pulse signals. For the convenience of comparison, the low-frequency perfusion indexes of the respective light wavelengths were subjected to trend line regression analysis by an exponential function. Among them, the rising trend of green light G and blue light B is faster than yellow green light YG and red light R, while the index of yellow green light YG is about 5 times larger than red light R. As shown in the fifth figure, the measurement results of the high-frequency perfusion index (P,) of different light wavelengths with the change of the spacing R are the average amplitude of the high-frequency pulsation signal in the 2 〇 second pulsation signal. The value, the high-frequency perfusion index of various wavelengths also uses the exponential function as the regression point to draw the trend line, and the four wavelengths of light all increase with the increase of the spacing R. The longer the wavelength of the light, the larger the trend. The more gradual, wherein the south frequency perfusion index is greater than 5% when the spacing R is from 3 milliseconds to 5 millimeters. The high-frequency pulsation signal is mainly used to analyze the main pulse number of the heart rate. Thus, the higher the ratio of the high-frequency pulsation signal to the DC pulsation signal, the more stable the high-frequency pulsation signal is, and the easier it is to detect the heart rate. The value of the frequency perfusion index is used to determine the amplitude of the high frequency pulsation signal of the measured portion, and the percentage of the corresponding high frequency pulsation signal and the pulsating DC signal is defined as the following high frequency 099126534 Form No. A0101 Page 10 / Total 30 Page 0992046543 -0 -------------(2) 201206397 Perfusion index (pih) Equation 2 is shown. When the wavelength of the first light 222 generated by the light source 122 is 560-580 nm, the corresponding pitch {{ is 3_4 mm. One of the sensing signals corresponds to a high frequency perfusion index of more than 5 〇/〇. As shown in the sixth figure, it is the relationship between the signal-to-noise ratio of the four optical wavelengths and the spacing R. The signal-to-noise ratio value of each measuring point is subjected to a trend regression analysis using a linear function, wherein the yellow-green light YG at a close distance The slope of the trend line of green light G and blue light & 要 is larger than that of red light R. And the signal-to-noise ratio of the yellow-green YG is about 7 dB higher than that of the blue light B and the green light G. The pitch R corresponds to the signal noise ratio SNR. When the pitch is 2 mm to 5 mm, the signal noise ratio is 10 decibels (dB) to 45 decibels (邙). Furthermore, the optical pulsation signal is affected by the physiological change of the sensed portion. The quality of the signal depends on the circuit variation of the photosensor 124 itself, so the signal-to-noise ratio (SNR) in the signal evaluation index is ) ' Generally, the vibration-size is defined as the signal-to-noise ratio. The equation is as shown in Equation 3 below. The decibel (dB) value is the unit of the noise-to-Q ratio. This indicator reflects the quality of the pulse signal. SNR=2〇xl Pavilion ίο jACmcal |Nojse|

Please refer to the seventh to ninth views, which are waveform diagrams of a preferred embodiment of the pulsation sensing device of the present invention for sensing the pulsation of the finger, forehead and forearm. As shown in the seventh to ninth embodiments, the pulse sensing device according to the present invention analyzes the sensing condition of the finger, the forehead, and the forearm, and analyzes the high frequency perfusion index, the signal noise ratio, and the transmittance. As shown in the seventh figure, it is a waveform diagram obtained by analyzing the high frequency perfusion index, and the invention is 099126534, the form number A0101, the 11th page, the total 30 page 0992046543-0 201206397, especially the effect of yellow-green light, so this embodiment is The pulse sensing device 1 〇 高频 高频 黄 黄 黄 黄 黄 黄 黄 黄 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉 脉And the changes in the situation, the measurement values of different parts are analyzed by exponential function. The high-frequency perfusion index of the three parts is increased with the increase of the spacing R. The ascending change of the site is the largest, the pure rising speed wheel of the index finger and the anterior heart is gentle and the south frequency weight flow index of the index finger is greater than the high (four) flow index of the inner side of the forearm. In the case of the pulse-sensing device, the pulse-sensing device 10 changes the signal-to-noise ratio of A, forehead, and the forearm with the spacing R as a yellow-green light. The linear trend regression analysis shows that the distance between the three parts is larger. The time signal noise ratio has a smaller trend, and the δίΐ noise ratio of the inner side of the forearm is the worst. As shown in the ninth figure, the pulse sensing device 10 is yellow and green light on the index finger, forehead, and When the light transmittance of the inner side of the forearm is changed with the spacing R, the tissue reflection light Α value when the index finger, forehead, and the inner tissue of the forearm are rich in sputum is divided by * blood content The tissue reflects the brightness value, taking the percentage and then using the exponential function to make the trend. The farther the distance R is, the lower the tissue light transmittance of the three parts has a tendency to decrease. The representative light transmission rate of the tissue is larger, and the tissue light transmittance trend line on the inner side of the forearm is larger than the tissue light transmittance trend line of the index finger. The tissue light transmittance of the two parts is about 25%. 099126534 as shown in the tenth Since the sensing signal of the present invention includes a high frequency pulsation signal, which can be applied to the sensing of the heart, the present invention is performed with a cardiac measuring instrument of the special form number A0101, page 12 of 30, 0992046543-0 201206397. Long-term simultaneous measurement, in order to prove that the present invention can be applied to the measurement of the heart'. This embodiment compares the electrocardiogram diagnosis report of the three-lead Huoer electrocardiograph with the high-frequency pulsation signal of the present invention, respectively, to record The 24-hour sensing results were analyzed, in which the upper waveform was an electrocardiogram (ECG), and the waveform below was a pulsation waveform (PPG), especially in the ECG waveform with continuous early atrial contraction (APC:

Atrial premature contraction) with early ventricular contraction (VPC: Ventricular premature contraction)

ECG waveform, and the ppG generated by the present invention has corresponding pulsation waveforms of APC and VPC, so the present invention can be used for a simpler power measurement to speed up the measurement of heart rate and simplify the initial electrocardiogram. The way of measurement. The pulse sensing device of the preferred embodiment of the present invention can detect the maximum signal intensity with minimum brightness, which is a large-scale high-frequency perfusion.

The index, and also allows the low frequency variation signal to have a large dynamic range, while the light penetration rate should be about 37% to get the best light absorption metric. Consider the measurement of the perfusion of the liquid perfusion; the fractional deceleration sensor should be designed to have a dynamic range of pulsating low-frequency fluctuation signals, and should avoid exceeding the upper limit of the detection of the instrument and saturating the signal, and It has a higher perfusion index and a better signal-to-noise ratio. It can be seen from the above that when the brightness of the four visible light sources is under the same conditions, the further the distance from the light source, the smaller the brightness of the scattered reflected light on the surface of the tissue. The smaller the light absorption coefficient and the scattering coefficient of the tissue, the larger the light distribution area of the light in the tissue. When selecting the wavelength of the light source, it is necessary to simultaneously measure the depth of the penetrating tissue and the light scattering reflection brightness of the wavelength at the measured portion. And the blood is selected as a light source having a large absorption coefficient for the wavelength of the light. When there is the same 099126534 0992046543-0 in the organization Form No. A0101 Page 13 / Total 30 Page 201206397 When the blood volume changes, it can produce strong brightness changes in the scattered reflected light on the tissue surface, and it is easier to measure by the photodetector. To the obvious pulsating communication signal component. In the relationship between the spacing R and the pulsation signal, when the spacing R is small, although the brightness of the tissue scattered reflected light is strong, the signal-to-noise ratio is better, but since the light penetration path is shorter, the blood diameter is smaller. Less, the blood absorption is also small, so the high-frequency perfusion index and the low-frequency perfusion index are small. Under normal conditions, the swing of the low-frequency fluctuation signal is much larger than the amplitude of the high-frequency pulsation signal. In the long-term measurement, it often causes a large fluctuation of the low frequency due to the change of the total perfusion flow of the tissue, so it is easy to cause the sensing signal. Saturation distortion. On the contrary, when the distance R is large, the light penetrates the path.

Longer, so the amount of blood in the light path tissue is more absorbed, and the brightness of the scattered light reflected by the tissue is weakened, so that the signal is smaller, so the signal is relatively poor, but the amount of blood in the path is also large, so Both the high frequency perfusion index and the low frequency perfusion index increase. When measuring the index finger in four different visible light, the high-frequency perfusion index is greater than 5%, only the yellow-green light source is yellow-green light, and the spacing R is between 3 mm and 3.5 mm. The index can reach 5% to 6%, in line with Pulse Design's good quality design conditions. ...... I

Similarly, the yellow-green light is used as the light source, and the signal-to-noise ratio of the index finger portion is gradually decreasing as the distance R is between 3 mm and 3.5 mm. The measurement results of the wavelengths of the different light sources in the finger portion show that the yellow-green light has a higher signal-to-noise ratio than the other colors when the spacing R is less than 4.6 mm, and the high-frequency perfusion index is also used when the spacing R is less than 3.3 mm. Higher than other colors. The measurement results of yellow-green light in different parts showed that the tendency of perfusion index and signal-to-noise ratio to change with the spacing R was also significantly different in different tissues due to different micro-vascular contents. The forehead is thinner than the soft tissue outside the skull. 099126534 Form No. A0101 Page 14 of 30 0992046543-0 201206397 In order to maintain the temperature of the head, the microvessel density is significantly higher to maintain high blood perfusion, so the light transmittance As the distance R increases, it will rapidly decay and the perfusion index will rise rapidly, so that the signal with the spacing R greater than 3.5 mm cannot be detected, but the spacing R can be measured up to 5 mm on the inside of the forearm and the finger. Light reflection signal.

The early cardiac contraction of the ECG waveform and pulsation waveform, as shown in the tenth figure, can be divided into early atrial contraction (APC) and early ventricular contraction (VPC). When the early contraction of the heart occurs, the heartbeat interval will be a short one. The long phenomenon and the time interval of early atrial contraction are shorter than the early contraction of the ventricle. It can be observed that the pulsation waveform of the enemies is observed. When the anterior atrial contraction occurs, the blood flow in the finger area is earlier than the heart name. Slightly less, the amplitude of the pulsation waveform at the early contraction of the atrium is smaller than the amplitude of the pulsation waveform at the early contraction of the ventricle. The comparison of the heart rate and the same chapter measurement experiment shows that the heart rate variability analysis trend of the light reflection pulse heart rate measurement can be consistent with the commercially available electrocardiograph, so it can be applied to the heart rate variability measurement of heart disease patients. Measurement analysis as an aid to cardiac function assessment. Light-reflective pulsation for a long time, Qi, can be used to record the pulsation waveform of the subject while in sleep, which contains many different physiological meanings such as sleep snoring, sleep breathing termination, etc., often combined with image recording, breathing Sensing, electrocardiogram, electromyogram, and brain wave map are used for simultaneous detection to study the application of sleep physiology. The light-reflective pulsation sensor is suitable for measurement on surfaces at different positions of the body. When using shorter-wavelength visible light as a light source, the diameter of the penetration path can be reduced and the size of the sensor can be reduced to facilitate the fixation, but it is also necessary The liquid solution is selected to have a high absorption wavelength to obtain a distinct optical pulsation signal. Therefore, the light absorption wavelength of ruthenium is around 560-580 nm. 099126534 Form No. A0101 Page 15 of 30 0992046543-0 201206397 The measurement can obtain a higher domain perfusion index. The distance between the light source and the sensor' affects both the perfusion index and the signal-to-noise ratio. When the spacing rule increases, the perfusion index increases with the increase of the light path, but the signal-to-noise ratio decreases with the brightness of the light reflection. reduce. The light-reflective pulsation sensor designed with the forehead as the sensing part under the condition of the minimum luminous power and the spacing R of 3_4 mm using the yellow-green light of the wavelength of 56G_58Q nanometer is convenient in use. Physical activity and less affected by changes in ambient temperature. The high-frequency perfusion index of the light-reflective pulsation sensor is 7.5%, and the signal-to-noise ratio is 28dB. The light transmittance of the tissue is 100%. The light absorption is near the linear range of the most accurate disk.丨 Probe. In summary, the present invention is a pulse sensing device that utilizes light that is reflected from skin tissue to affect the change of light path by pulsation changes of the blood vessel, and further learns cardiovascular pulsation by The integrated circuit makes the invention degenerate, and can quickly know and judge the cardiovascular pulsation, so as to make a preliminary Qing, therefore, the present invention improves the efficiency of the judgment of the heart-to-tube pulsation, and can increase the convenience of the pulse measurement. Sex. Therefore, the present invention is actually - has _ sex, progress and available to the industrial users 'should be in line with the _ full-time patent towel, please ask for the money, the epidemic according to the law, the invention of the special shot, please analyze the 钧 bureau to grant the patent as soon as possible, to the sense Prayer 0, but the above is only the present invention - the preferred embodiment, and is not intended to be used in the scope of the invention, which is equivalent to the shape, structure, features and spirit described in the patent application scope of the present invention. Variations and modifications are to be included in the scope of the patent application of the present invention. BRIEF DESCRIPTION OF THE DRAWINGS FIG. 1A is a block diagram of an embodiment of a pulse sensing device of the present invention. FIG. FIG. 2 is a block diagram of another preferred embodiment of the present invention; FIG. 2B is a schematic structural view of another preferred embodiment of the present invention; 3 is a waveform diagram of a preferred embodiment of the present invention; a fourth diagram is a waveform diagram of another preferred embodiment of the present invention; and a fifth diagram is a waveform diagram of another preferred embodiment of the present invention; 6 is a waveform diagram of another preferred embodiment of the present invention; seventh embodiment is a waveform diagram of another preferred embodiment of the present invention; and FIG. 8 is a waveform diagram of another preferred embodiment of the present invention Figure 9 is a waveform diagram of another preferred embodiment of the present invention; and a tenth diagram is a waveform diagram of another preferred embodiment of the present invention.

[Main component symbol description] [0006] 10 pulse sensing device 12 sensing module 122 light source 124 light sensor 126 sensing circuit 14 control processing circuit 16 display unit 18 power supply 20 circuit substrate 22 fixing member 30 living body 32 skin tissue 322 Epithelial tissue 099126534 Form No. A0101 Page 17 of 30 0992046543-0 201206397 324 326 Subcutaneous tissue of dermis tissue 099126534 Form No. A0101 Page 18 of 30 0992046543-0

Claims (1)

201206397 VII. Patent application scope: 1 - a pulse sensing device, comprising: - a light source 'which is disposed on a skin tissue of a living body and generates at least a first light to be irradiated to the skin tissue, the first The light is reflected by the skin tissue to form a second light, wherein a volume change of blood of at least one blood vessel in the skin tissue is associated with a change in brightness or a change in wavelength of the second light; - a light sensor disposed on the skin tissue The light sensor has a spacing from the light source, the light sensor receives the second light; and a sensing circuit is coupled to the light sensor and received according to the light sensor The second light produces a sensing signal; the spacing is associated with the wavelength or brightness of the second aperture. 2. The pulse sensing device of claim 1, further comprising: - a control processing circuit 'connecting the sensing circuit and incorporating the sensing signal' to generate an output signal according to the sensing signal The output signal corresponds to the pulse change; ··· '·. a display unit according to the output signal corresponding to the second round of the image; and a power source 'generating a plurality of power signals and respectively transmitting to the light source, the light sensing The sensing circuit, the control logic circuit and the display unit. 3. The pulse sensing device of claim 1, wherein the sensing signal comprises a low frequency perfusion index, and the low frequency perfusion index is greater than 5% when the spacing is from 3 mm to 5 mm. 4. The pulse sensing device of claim 1, wherein the sensing signal comprises a high frequency perfusion index, and the high frequency perfusion index is greater than 5 when the spacing is from 3 mm to 5 mm. /〇. 5. The pulse sensing device according to claim 1, wherein the spacing 099126534 form number A0101 page 19/total 30 page 0992046543-0 201206397 corresponds to a signal noise ratio 'when the spacing is 2 mm The signal noise ratio is 10 decibels (dB) to 45 decibels (dB) up to 5 mm. 6. The pulse sensing device of claim 1, wherein the first light and the second light have a wavelength ranging from 400 nm to nanometer. 7. The pulse sensing device of claim 1, wherein the spacing ranges from 2 mm to 8 mm. The pulse sensing device of claim 1, wherein the first light has a wavelength of 560 - 580 nm, and the corresponding spacing is 3 _ 4 mm, the sensing One of the signals corresponds to a high frequency perfusion index of more than 5%. 9. The pulse sensing device of claim 1, wherein the wavelength of the light is proportional to the spacing. The pulse sensing device of claim 1, wherein the brightness of the light is inversely proportional to the distance. 11. The pulse sensing device of claim 1, wherein the amplitude change of one of the sensing signals is related to a volume change of blood of the blood vessel. 099126534 Form No. A0101 Page 20 of 30 0992046543-0