CN2798135Y - Glasses to monitor physiological system parameters - Google Patents

Abstract

A kind of glasses for monitoring physiological system parameters, using glasses or diving goggles to realize the measurement of multiple key physiological parameters, including: the usual glasses structure as the carrier of other components; a biological signal control switch located at a specific position of the glasses structure, the biological The signal control switch responds to the specific biological signal sent by the user's body to generate an activation signal; the sensor unit is installed at an appropriate measurement position on the user's body, and the sensor unit is connected to the biological signal control switch in a wired or wireless manner to receive and respond The starting signal starts to measure the appropriate physiological signals of the human body; the processor unit located in the glasses structure is connected to the sensor unit in a wired or wireless manner, receives the measured physiological signals from the sensor unit and calculates The physiological parameter information. The device is simple to operate and easy to use, and can provide users with real-time continuous monitoring of safe, economical and practical non-destructive physiological parameters.

Description

Glasses to monitor physiological system parameters

technical field

The utility model relates to a monitoring device/device for multiple physiological parameters, in particular to a real-time continuous monitoring device/device for realizing multiple key physiological parameters.

Background technique

The monitoring of physiological parameters, especially the monitoring of changes in key physiological parameters reflecting the function of the cardiovascular system can provide users with timely information feedback in order to understand their health conditions. Statistics from the American Heart Association show that 16,600,000 people worldwide die from cardiovascular disease every year, and it has become the number one killer of human health. Physiological parameters that reflect the function of the cardiovascular system usually include: heart rate, heart rate variability, blood pressure, blood oxygen saturation, and respiratory rate. Daily monitoring of these physiological parameters can enable early detection and early treatment of cardiovascular diseases that may lead to serious consequences. The measurement of these physiological parameters is usually completed by different instruments or devices, that is, the measurement of each parameter requires an independent device. Like this, not only increased user's expenses, but also not convenient for daily use.

Currently, most monitoring devices suitable for everyday use come in the form of watches or other portable devices. This type of watch-type device can mainly provide monitoring of heart rate. The user can obtain the above physiological information continuously and in real time by wearing the watch. However, the information that the device can provide to characterize the function of the cardiovascular system is relatively limited, and is limited to the monitoring of heart rate information. Moreover, reading information from the watch may hinder the ongoing activities of the user in some occasions.

Other devices that can provide more parameters that characterize the cardiovascular system are usually relatively large in size and cannot be worn around in order to obtain these physiological parameters in real time. Therefore, it is particularly important to develop a device that can be worn on the body and can provide real-time status information of multiple cardiovascular systems without interference.

By wearing glasses, the user obtains relevant information reflecting the state of motion, such as the technology of motion time, motion distance and motion speed, etc., which can be found in published US patents. A kind of glasses-type sports timing device with electronic display is disclosed as US Patent No. 4,526,473. US Patent Nos. 4,751,691, 5,103,713 and 5,258,785 disclose related eyewear design structures, especially methods for display devices therein. However, the above-mentioned patents only provide different ways of how to realize the display function on the glasses, but do not involve how to apply the structural design of the glasses to monitor the physiological parameters that represent the physiological state.

U.S. Patents 5,585,871, 5,813,990 and 6,431,705 proposed that by wearing glasses, not only the information of the exercise state such as exercise time, exercise distance, and exercise speed can be measured, but also the temperature and heart rate can be used to measure parameters that characterize the physiological state. In US patents 5,585,871 and 6,431,705, the heart rate measuring device is integrated into the design of the glasses. The sensor detects pressure changes or pulse waves through contact with the user's temple or bridge of the nose to obtain heart rate information, and then the relevant information is projected to the wearer's visual area through optical fiber transmission. Since the signals obtained from the above two measurement locations are limited, the above location selection is not suitable for the measurement of other physiological parameters. In US Patent No. 5,813,990, a sensor for detecting pulse waves is clipped on the user's earlobe, and the heart rate is calculated by counting the number of pulses that can be detected in one minute. The pulse wave detection sensor used in this patent is an infrared photosensitive transistor and a photodetector, which detects the pulse wave through transmission.

Although continuous and real-time heart rate monitoring can be achieved through the above three patents, the switch control signal of the glasses has to be operated manually, so it cannot truly realize non-interfering physiological parameter monitoring. Moreover, in practical daily applications, only knowing the heart rate information is not enough. Other parameters that reflect changes in the state of the cardiovascular system, such as blood pressure, blood oxygen saturation, and respiratory rate, are also very important for users to understand their physical conditions. However, there is currently no wearable glasses device that can truly monitor multiple physiological parameters in real time without interference.

Utility model content

The technical problem to be solved by the utility model is to propose the application of glasses or diving goggles to realize the values of multiple key physiological parameters representing the state of the cardiovascular system. In daily use, the wearers can continuously obtain the values of the above physiological parameters in real time without interfering with the monitoring device, so that their daily activities are not hindered.

The technical solution adopted by the utility model is to provide a kind of glasses for monitoring physiological system parameters, including: a common glasses structure as the carrier of other components; a biological signal control switch located at a specific position of the glasses structure, and the biological signal control switch responds to The specific biological signal sent by the user's body is used to generate an activation signal; the sensor unit is suitable for being installed at an appropriate measurement position of the user's body, and the sensor unit is connected with the biological signal control switch in a wired or wireless manner to receive and respond to the biological signal. The starting signal starts to measure the appropriate physiological signals of the human body; and the processor unit located in the glasses structure is connected with the sensor unit in a wired or wireless manner, receives the measured physiological signals from the sensor unit and calculates the Physiological parameter information.

Preferably, the nondestructive measurement of multiple physiological parameters in the present invention is realized by using a photoelectric sensor to detect photoplethysmographic signals on the ear. The measurement of heart rate can be realized by calculating the time between the peaks of a column of photoplethysmographic signals; the measurement of blood pressure can be realized by calculating the time delay between two columns of photoplethysmographic signals, that is, the pulse wave transit time; or by using The upper arm blood pressure waveform corrects the photoplethysmographic signal waveform obtained from the ear to calculate the blood pressure value. The measurement of blood oxygen saturation can be realized by using the principle of pulse oximeter. The measurement of respiratory rate is obtained by filtering the photoplethysmographic signal within a certain frequency band.

Unlike previous devices, by fixing photoelectric sensors on the user's ears, the device can measure not only heart rate and heart rate change rate, but also blood pressure, blood pressure change rate, blood oxygen saturation and respiratory rate. Since the above sensor is small in size and light in weight, it will not have a great impact on the volume and weight of the whole device.

The utility model also includes a control mode of a switch for measuring physiological parameters through biological signals. Because the physiological parameter measurement of the utility model is completed by using glasses or diving goggles, the biological signals used for switch control are all given priority to the signals obtained near the eyes. This method can avoid manual operation, truly achieve non-interference measurement, and at the same time reduce the volume and weight of the device to a certain extent, and reduce power consumption.

The beneficial technical effect of the utility model is: in order to monitor multiple physiological parameters without interference through the wearable device, the utility model proposes the application of glasses or diving goggles to realize the measurement of multiple key physiological parameters representing the state of the cardiovascular system . Because the utility model uses the biological signal as the switch control signal instead of the traditional manual method, the user can truly achieve completely interference-free measurement by wearing glasses or diving goggles, thereby making up for the shortcomings of all the above-mentioned devices.

Description of drawings

Fig. 1a is a perspective view of the structure of glasses in the first preferred embodiment of the present invention.

Fig. 1b is a perspective view of the structure of glasses in the second preferred embodiment of the present invention.

2a and 2b are schematic diagrams of sensors used in different positions in the present invention.

3a and 3b are schematic diagrams of placement of two electrodes used for measuring electrooculogram signals.

FIG. 4 is an explanatory diagram of an electrooculography signal.

5a-5d are schematic diagrams for realizing the measurement of various physiological parameters in the utility model.

Detailed ways

The advantages and purposes of the utility model will be illustrated by the following drawings and descriptions of the embodiments.

The glasses or diving goggles described in the utility model are an integrated device. The device can provide users with timely feedback of physiological parameter information, and is especially suitable for people who need daily or frequent monitoring of physiological parameters. Relevant physiological parameter information can be communicated to the user through visual or acoustic means. Hereinafter, an embodiment is described with glasses.

As shown in Figures 1a and 1b, the integrated device includes, in addition to the usual spectacle structure, spectacle frame 101, spectacle frame 112 and lens 113, a battery 102 as a power source for the entire device; sensor arrays 115, 116, 117, They can be comfortably in contact with the user's ear 201 through a clip to obtain the required physiological signals; the printed circuit units 104 and 106 process the obtained signals, including an amplification unit and a filter unit, and convert the required Miniaturization of the circuit, while the circuit includes a wireless data transmission unit that transmits the obtained signals from the sensor arrays 115, 116 and 117 to the corresponding circuits 104 and 106; the channel 111 is placed to connect the printed circuit units 104 and 106 Electric wire; Microprocessor unit 107, carry out the calculation and data storage of physiological parameters; Function selection and control unit 109, can choose to measure one or more physiological parameters simultaneously and choose to obtain information by visual or sound; A plurality of information feedback devices in the glasses structure, which are electrically connected to the function selection and control unit to allow the user to select one of the plurality of information feedback devices to provide information feedback, and the information feedback device may include a display unit 103 And the information viewing mode 110, so that the user can see the measurement results of the physiological parameters in the visible range; it can also include a sound unit 114, which can be an earplug, and the measurement results of the physiological parameters obtained can be communicated to the user in the form of sound ; Switch control 108, manually control the switch of the whole device.

In order for the eyewear structure to be suitable for everyday activities, it must be strong, shock-resistant and lightweight. The lens 113 can be made of light resin material, while the frame 112 and the frame 101 can be made of polypropylene injection molding material. The sensor 105 , the battery 102 , the printed circuit units 104 and 106 , the microprocessor unit 107 , the display unit 103 and the sound generating unit 114 may be mounted on the frame 112 . In order to balance the weight of the whole glasses, the circuit can be divided into two parts 104 and 106, which are placed on the left and right sides of the frame 112 respectively. The sensor 105 , the battery 102 , the display unit 103 and the sound unit 114 can be respectively placed on the left and right sides of the mirror frame 112 according to the requirement of weight balance. In addition to computing corresponding physiological parameters and storing data using the received signals, the microprocessor unit 107 is also connected to the display unit 103 and the sound unit 114 to control the transmission of information.

In addition to the circuits that can be placed on the frame 112, part of the printed circuit units 104 and 106 can also be placed on the sensor arrays 115, 116 and 117 to process the obtained physiological signals, including amplification and filtering, and then from the sensor arrays 115, 116 and 117 The wireless data is transmitted to the remaining printed circuit units 104 and 106 placed on the spectacle frame 112, and the microprocessor unit 107 is used to calculate physiological parameters and store data.

In addition, the printed circuit units 104 and 106, the microprocessor unit 107, the display unit 103, the sound unit 114, the display unit 103 and the information viewing mode 110 can all be integrated in the sensor arrays 115, 116 and 117 to reduce the weight of the glasses , to provide users with more comfortable monitoring of physiological parameters.

The function selection and control unit 109 can be placed on the spectacle frame 112 to control the use mode of the spectacle through buttons. For example, you can choose to obtain physiological parameter information visually or by sound. The visual method can obtain real-time information update, while the sound method can only obtain intermittent information update, and the time interval for information update can be selected by oneself when using it. At the same time, you can also choose to update the information only for a specified parameter when using it. In addition to being used to communicate updated information, the sound mode also has an alarm function. If a limit value is preset for a certain physiological parameter index during use, then when the parameter exceeds the preset value, the system will give an alarm prompt.

There are many options for the imaging mode of the display unit 103, such as LCD, LED, and CRT, and the details thereof can be found in the aforementioned US patent. Similarly, the specific implementation details of the information viewing mode 110 can also be found in the aforementioned US patents, and will not be repeated here. The sound generating unit 114 can be placed on the spectacle frame 112 near the ear or in the user's cochlea (using earplugs).

The sensor arrays 115, 116 and 117 are composed of at least three photosensitive transistors and at least three photodetectors, and the specific positions of the sensor arrays 115, 116 and 117 in contact with the ear 201 are shown in Fig. 2a. Among the three phototransistors, the upper wavelength 115 is selected in the infrared wavelength range, while the lower two 116 and 117 wavelengths are selected in the infrared and red wavelength ranges respectively. Generally, 940nm can be selected in the infrared wavelength range, and 660nm can be selected in the red wavelength range. Corresponding photodetectors are elements sensitive to light in the wavelength range mentioned above. Since the tissue structure at the ear 201 is relatively thin, the phototransistor preferably works in a transmission mode, and a stronger signal can be obtained in this mode. But it can also work in reflection. The detected signal is a photoplethysmographic signal, which is synchronized with the beating of the heart, and the parameters extracted from it can reflect the health of the cardiovascular system.

In the present invention, the sensors 116 and 117 located at the lower part of the ear can have different contact positions with the ear. Since the photoplethysmographic signal is easily disturbed by motion noise, we made an optimal choice for the position of the sensor array in contact with the ear. The position of the sensor 117 in Fig. 2a is selected in the utility model, and its position is far away from the face. The position of the sensor 117 in Fig. 2b is closer to the face. We found experimentally that locations farther from the face are less affected by motion noise. Therefore, in this embodiment, the position of the sensor 117 is preferably far away from the face, and its position range is about 0.5-1.0 cm away from the face.

The utility model not only can control the switch of the physiological parameter measurement through the button manually, but also can use the biological signal sent by the body to control the switch. This design reduces manual operations and therefore reduces disturbance to the user during measurements. It also provides the possibility to reduce component consumption and power consumption. Because the physiological parameter measurement of the utility model is completed by using glasses, the biological signals used for switch control are all given priority to the signals obtained near the eyes.

In preferred embodiment 1, the pressure change signal is used as the biological signal for controlling the switch, and its acquisition is accomplished through a pressure sensor 105a. The pressure sensor 105 a is installed in the mirror frame 112 . The tightness of the mirror frame 112 is adjustable to ensure that the pressure sensor 105a is in effective contact with the user's face. When the user opens and closes the eyes, the muscles around the eyes are tensed, and the pressure sensor 105a will obtain a corresponding pressure change signal. After the pressure signal is amplified, filtered and/or re-amplified by the circuit units 104 and 106, it can be used as a switch control signal to activate the glasses to measure one or more physiological parameters.

In the second preferred embodiment, the electrooculogram signal is used as the biological signal for controlling the switch, and its acquisition is completed through the three electrodes 105b. When the eye moves, the electrical signals between the cornea and retina change accordingly. In the human body, this electrical energy is typically 0.05 to 3.5mV, and is roughly proportional to the distance the eye moves. This potential information is called the electrooculogram signal. Just stick five electrodes on the user's face, and the electrooculogram signal can be obtained. By measuring this signal, eye movement can be estimated. When measuring, one pair of electrodes is placed on the left and right sides of the eye to measure the horizontal movement of the eyeball; the other pair is placed above and below the eye to measure the vertical movement of the eyeball, and the remaining one is placed on the forehead as a reference point . The specific practice of the measurement circuit of the electrooculogram signal is described in detail in the document Automatic Detection and Operant Reinforcement ofSlow Potential Shifts, J.M.Siegel, M.B.Sterman and S.Ross, Physiology&Behavior, 23, 1979, 411-413, so here No longer. In addition, those skilled in the art can understand that the electrodes for measuring the reference signal can be omitted, and only a pair of electrodes are used to measure the electrooculogram signal to achieve the above purpose. Also, one of the aforementioned pair of electrodes may be grounded, so in practice, only one electrode can be used to measure the electrooculogram signal.

Because the present invention only uses the electrooculogram signal as a mode of switch control, instead of measuring eyeball movement, only three electrodes 105b are needed. One pair is used to measure electrical signals and can be placed horizontally or vertically, while the other serves as a reference point. These electrodes 105b are installed in the mirror frame 112 . The tightness of the mirror frame 112 is adjustable to ensure that the electrode 105b is in effective contact with the user's face. Taking a pair of electrodes 105b placed horizontally as an example, as long as the user moves the eyeball to the left or right three times continuously, the obtained electrooculogram signal is amplified, filtered and/or re-amplified by the circuit units 104 and 106 , can be used as a control signal of the switch to activate the glasses to measure one or more physiological parameters. Taking a pair of electrodes 105b placed in a vertical manner as an example, as long as the user moves the eyeball up or down three times continuously, the obtained electrooculogram signal is amplified, filtered and/or re-amplified by the circuit units 104 and 106 , can be used as a control signal of the switch to activate the glasses to measure one or more physiological parameters.

3a and 3b are schematic diagrams of placement of two electrodes used for measuring electrooculogram signals. As seen in FIG. 3a, a pair of electrodes 105b1 and 105b2 for measuring electrooculogram signals can be placed horizontally at the temple 301, while the electrode 105b3 as a reference point is placed on the forehead 302. As seen in FIG. 3b, the electrooculography signal electrodes 105b1 and 105b2 can be placed vertically above and below any eye 303, while the reference point electrode 105b3 is placed just in front of the forehead 302. These electrooculogram signal electrodes are made of steel sheets and installed in the frame 112 .

FIG. 4 is an explanatory diagram of an electrooculography signal. Taking the horizontal placement method as an example, when the eyeball does not make any movement relative to the reference point, the potential information is zero. The weak EO information changes with how much the eye moves relative to the reference point. For example, when the eyeball moves to the right, it produces positive potential information, and when the eyeball moves to the left, it produces negative potential information.

The principle of realizing the measurement of various physiological parameters in the present invention will be described below in conjunction with FIGS. 5a to 5d.

In the utility model, the measurement of physiological parameters is realized by photoplethysmography. Photoplethysmography is easy and safe to use, and will not cause discomfort to the user if used for a long time. Devices that detect signals using photoplethysmography typically include a sensor unit that has a light-emitting device, such as a phototransistor, that directs light onto a surface at the measurement location, such as a finger, earlobe, or forehead, and a light-receiving device, such as a photoelectric A detector that detects light reflected or transmitted from the measurement location. As arterial pulsations cause changes in blood flow in vessels, there are corresponding changes in the absorption, reflection and scattering of light. Therefore, the light intensity detected by the light receiving device also changes accordingly, and the light intensity signal can be further processed and analyzed after being converted into an electrical signal.

As previously mentioned, the signals detected by the sensor arrays 115, 116 and 117 are photoplethysmographic signals, which are synchronized with the beating of the heart. Therefore, as shown in FIG. 5 a , the heart rate value can be calculated by calculating the time interval (intervali) between two adjacent peaks or two adjacent bottom points of the signal. In order to reduce the calculation error, we use the average (Ave-interval) of ten time intervals to calculate the instantaneous heart rate (HR), as shown in formulas (1) and (2). From this time interval it is also possible to calculate the rate of heart rate change, which is the standard deviation of a certain number of time intervals.

$\begin{array}{cc}\mathrm{<span\; class="notranslate">\; Ave.</span>}<span\; class="notranslate">\; \_</span>\mathrm{<span\; class="notranslate">\; interval</span>}<span\; class="notranslate">\; =</span>\frac{\underset{\mathrm{<span\; class="notranslate">\; i</span>}<span\; class="notranslate">\; =</span>\mathrm{<span\; class="notranslate">\; 1</span>}}{\overset{\mathrm{<span\; class="notranslate">\; no</span>}}{\mathrm{<span\; class="notranslate">\; \&Sigma;</span>}}}{\mathrm{<span\; class="notranslate">\; interval</span>}}_{\mathrm{<span\; class="notranslate">\; i</span>}}}{\mathrm{<span\; class="notranslate">\; no</span>}}& \mathrm{<span\; class="notranslate">\; no</span>}<span\; class="notranslate">\; =</span>\mathrm{<span\; class="notranslate">\; 10</span>}<span\; class="notranslate">\; -</span><span\; class="notranslate">\; -</span><span\; class="notranslate">\; -</span><span\; class="notranslate">\; (</span>\mathrm{<span\; class="notranslate">\; 1</span>}<span\; class="notranslate">\; )</span>\end{array}$

$\mathrm{<span\; class="notranslate">\; HR</span>}<span\; class="notranslate">\; =</span>\frac{\mathrm{<span\; class="notranslate">\; 1</span>}}{\mathrm{<span\; class="notranslate">\; Ave.</span>}<span\; class="notranslate">\; \_</span>\mathrm{<span\; class="notranslate">\; interval</span>}}<span\; class="notranslate">\; \&times;</span>\mathrm{<span\; class="notranslate">\; 60</span>}<span\; class="notranslate">\; -</span><span\; class="notranslate">\; -</span><span\; class="notranslate">\; -</span><span\; class="notranslate">\; (</span>\mathrm{<span\; class="notranslate">\; 2</span>}<span\; class="notranslate">\; )</span>$

Since the two main light-absorbing substances in blood, oxyhemoglobin and hemoglobin, absorb light differently in the red light range and infrared light range, arterial blood oxygen saturation can be determined by using two wavelengths of light. As mentioned above, placing phototransistors with different wavelengths, that is, two phototransistors 116 and 117 for red light and infrared light, at the same measurement position, can obtain two columns of photoplethysmographic signals at the same time. The two columns of signals are first filtered and amplified. Then separate the DC and AC parts of the red light and infrared light signals, and then according to the principle of the pulse oximeter, we can get the arterial blood oxygen saturation through these two signals. Its specific circuit implementation can be found in "Designof Pulse Oximeters" by J G Webseter. Figure 5b presents a schematic diagram of the AC portion of the photoplethysmographic signal obtained with light of different wavelengths. The calculation of arterial oxygen saturation is done by the following formula:

$\mathrm{<span\; class="notranslate">\; R</span>}<span\; class="notranslate">\; =</span>\frac{\frac{{\mathrm{<span\; class="notranslate">\; AC</span>}}_{\mathrm{<span\; class="notranslate">\; R</span>}}}{{\mathrm{<span\; class="notranslate">\; DC</span>}}_{\mathrm{<span\; class="notranslate">\; R</span>}}}}{\frac{{\mathrm{<span\; class="notranslate">\; AC</span>}}_{\mathrm{<span\; class="notranslate">\; IR</span>}}}{{\mathrm{<span\; class="notranslate">\; DC</span>}}_{\mathrm{<span\; class="notranslate">\; IR</span>}}}}<span\; class="notranslate">\; -</span><span\; class="notranslate">\; -</span><span\; class="notranslate">\; -</span><span\; class="notranslate">\; (</span>\mathrm{<span\; class="notranslate">\; 3</span>}<span\; class="notranslate">\; )</span>$

SpO ₂ =110-25R (4)

Among them, AC _R represents the AC part of the photoplethysmography signal obtained by red light, DC _R represents the DC part of the photoplethysmography signal obtained by red light; AC _IR represents the AC part of the photoplethysmography signal obtained by infrared light, DC _IR stands for the DC portion of the photoplethysmographic signal obtained from infrared light. By obtaining the ratio (3) between them and using the empirical formula (4), the arterial blood oxygen saturation can be obtained.

Calculation of blood pressure can be done in two ways:

Embodiment one

By combining two phototransistors with the same wavelength at different positions, we can obtain two columns of photoplethysmographic signals with a certain time delay between the two signals, as shown in Figure 5c. This time delay is called the pulse wave transit time. For healthy adults, the time delay between the photoplethysmographic signals measured from the upper and lower parts of the ear is 20-30 milliseconds in the quiet state, and 10-20 milliseconds in the moving state. Many documents and patents have introduced the method of calculating blood pressure using the theory of pulse wave transit time. Pulse wave transit time is the time difference between a pulse arriving at two different points as it travels along the same artery. This time delay has been proved to be related to blood pressure, and it will decrease with the increase of blood pressure. Therefore, by using a standard blood pressure instrument to calibrate the relationship between the pulse wave transit time and blood pressure, that is to find the relationship between the pulse wave transit time and blood pressure. This time can then be used to estimate the blood pressure value. For the specific calculation method, please refer to US Patent Nos. 4,869,262 and 5,649,543, etc., which will not be repeated here.

Usually the pulse wave transit time is determined jointly by the electrocardiographic signal and the photoplethysmographic signal obtained from the finger, and its sampling frequency is usually selected as 1000 Hz. The pulse wave transit time ranges from about 100 to 200 milliseconds, which is longer than the pulse wave transit time obtained from the ear. Therefore, when using this method, how to improve the resolution of the system without increasing the system hardware and/or power consumption is very critical. Although the photoplethysmographic signal can still be detected by reducing the sampling frequency to 1000 Hz, the sampling frequency of 1000 Hz does not provide enough resolution for the pulse wave transmission time obtained from the ear, which is only 20-30 milliseconds , so the optimized sampling frequency in this embodiment is selected as 2000-3000 Hz to improve the resolution.

Embodiment two

Another way to calculate blood pressure is to use the upper arm blood pressure waveform to correct the photoplethysmographic signal waveform obtained from the ear. Therefore, only one series of waveforms, that is, one sensor, is used to obtain blood pressure information. In this case the sensor 115 need not be used. Published literature points out that there is a certain relationship between the radial artery blood pressure waveform and the waveform of the photoplethysmographic signal obtained from the finger. See the literature Modeling the relationship between peripheral bloodpressure and blood volume pulses using linear and neural networksystem identification techniques, John Allen and Alan Murray, Physiol.Meas., 20, 1999, 287-301 and Noninvasive assessment the comprehensive assessment of fluthedigital pressure pulse, Sandrine C. Millasseau and Franck G. Guigui, et al., Hypertension, 36, 2000, 952-956. Similarly, a transfer function characterizing the relationship between the radial artery blood pressure waveform and the photoplethysmographic signal at the ear is also available. The transfer function can be obtained by comparing the radial artery blood pressure waveform with a device capable of continuous blood pressure measurement from the wrist and comparing it with the photoplethysmographic signal waveform obtained at the ear to complete the calibration step. It should be pointed out that this calibration process is object-dependent. Therefore, each user should be calibrated separately before use. The specific calculation method can be found in US Patent 6,616,613.

As shown in Fig. 5d, the photovolume signal obviously also includes breathing information. The respiratory rate of a healthy adult is 10 to 20 breaths per minute. The method of using photoplethysmographic signals to extract respiratory frequency has been widely discussed in the literature in recent years, such as the literature Respiratory rhythm detection with photoplethysmographic methods, Dieter Barschdorff and Wei Zhang, Proceedings of IEEE-EMBS, pp912-913, 1994 and Monitoring of heart and respiratory rates by photoplethysmography using a digital filtering technique, K. Nakajima, T. Tamura and H. Miike, Med. Eng. Phys. Vol.18, No.5, pp365-372, 1996. Select an appropriate filter for low-pass filtering to obtain the respiratory waveform and calculate the respiratory frequency.

Claims (22)

1. glasses of monitoring the physiological system parameter, comprising: common Glasses structure is as the carrier of other elements; It is characterized in that, also comprise the bio signal gauge tap that is positioned at described Glasses structure ad-hoc location, enabling signal to take place in the particular organisms signal that described bio signal gauge tap response user's body sends; Be installed on the sensor unit of user's body measurement position, described sensor unit links to each other in wired or wireless mode with described bio signal gauge tap and begins to measure the suitable physiological signal of human body to receive and to respond described enabling signal; With the processor unit that is arranged in described Glasses structure, link to each other in wired or wireless mode with described sensor unit, receive from measuring of described sensor unit physiological signal and calculate described physiological parameter information.

2. the glasses of monitoring physiological system parameter as claimed in claim 1 is characterized in that, further comprise: be arranged in described Glasses structure and with the described processor unit printed circuit unit and function selecting and the control module that link to each other of electricity each other.

3. the glasses of monitoring physiological system parameter as claimed in claim 2, it is characterized in that described printed circuit unit comprises a wireless data transmission unit and links to each other with described processor unit point and carry out the information transmission with described sensor unit with wireless communication mode.

4. the glasses of monitoring physiological system parameter as claimed in claim 2 is characterized in that, described function selecting and control module comprise that the button that places described Glasses structure outside is to allow the user and select one or simultaneously a plurality of physiological parameters to be measured.

5. the glasses of monitoring physiological system parameter as claimed in claim 4, it is characterized in that, also comprise a plurality of information feedback devices that place described Glasses structure, it is electrically connected with control module to allow the user to select one of described a plurality of information feedback devices so that information feedback to be provided with described function selecting.

6. the glasses of monitoring physiological system parameter as claimed in claim 1 is characterized in that, described sensor unit comprises photoelectric sensor and in order to the device of fixation of sensor unit on the measuring position.

7. the glasses of monitoring physiological system parameter as claimed in claim 6 is characterized in that, described photoelectric sensor comprises at least two photistors and at least two photoelectric detectors.

8. the glasses of monitoring physiological system parameter as claimed in claim 7 is characterized in that, described two photistors comprise a ruddiness and a ruddiness photistor.

9. the glasses of monitoring physiological system parameter as claimed in claim 1 is characterized in that, described bio signal gauge tap comprises that at least one electrode is to obtain an eye movement electrograph trace signal.

10. the glasses of monitoring physiological system parameter as claimed in claim 1 is characterized in that, described bio signal gauge tap comprises at least one pair of electrode to obtain an eye movement electrograph trace signal, and described electrode flatly is placed on the mirror holder both sides.

11. the glasses of monitoring physiological system parameter as claimed in claim 1, it is characterized in that, described bio signal gauge tap comprises at least one pair of electrode to obtain an eye movement electrograph trace signal, and described electrode is placed vertically in picture frame one side, obtains signal from an eyeball.

12. the glasses as claim 10 or 11 described monitoring physiological system parameters is characterized in that described bio signal gauge tap comprises that also another electrode is with measuring reference signals.

13. the glasses of monitoring physiological system parameter as claimed in claim 1 is characterized in that, described bio signal gauge tap is controlled by near the pressure signal that muscle activity obtained the eyes.

14. the glasses of monitoring physiological system parameter as claimed in claim 13 is characterized in that, described bio signal gauge tap is controlled by the folding of eyes.

15. the glasses of monitoring physiological system parameter as claimed in claim 13 is characterized in that, described pressure signal is obtained by at least one pressure transducer.

16. the glasses of monitoring physiological system parameter as claimed in claim 15 is characterized in that, described pressure transducer places any side of mirror holder.

17. the glasses of monitoring physiological system parameter as claimed in claim 1 is characterized in that, described measuring position is the top and the ear-lobe of human body ear.

18. the glasses of monitoring physiological system parameter as claimed in claim 2 is characterized in that, described processor unit sample frequency is the 2000-3000 hertz.

19. the glasses of monitoring physiological system parameter as claimed in claim 2, it is characterized in that, described processor unit links to each other with the control module electricity with described function selecting, described processor unit calculates described physiological parameter, and the described physiological parameter that calculates is passed to described function selecting and control module.

20. the glasses of monitoring physiological system parameter as claimed in claim 2 is characterized in that described printed circuit unit comprises filter unit and amplifying unit.

21. the glasses of monitoring physiological system parameter as claimed in claim 5 is characterized in that, described information feedback device comprises a display unit.

22. the glasses of monitoring physiological system parameter as claimed in claim 5 is characterized in that, described information feedback device comprises a phonation unit.

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