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    • 专利摘要:
    personal health data collection. the present invention relates to a personal portable monitor, comprising a device for acquiring signals, which can be used to derive a measure of a parameter relating to the user's health, the signal acquisition device being integrated with a computing device. personal laptop. the present invention also provides a signal acquisition device, adapted to be integrated with a personal portable computing device, to produce a personal portable monitor as defined above.
    公开号:BR112013033461B1
    申请号:R112013033461-4
    申请日:2012-06-26
    公开日:2021-07-27
    发明作者:Christopher Elliott；Mark-Eric Jones；Mark Bennett；Mikhail Nagoga
    申请人:Leman Micro Devices Sa；
    IPC主号:
    专利说明:

    FIELD OF THE INVENTION
    [0001] The present invention relates to means for collecting personal health data. In particular, the invention relates to a personal portable monitor (hereinafter "a PHHM"), comprising a signal acquisition device for acquiring signals, which can be used to derive one or more measurements of parameters related to a user's health. , the signal acquisition device being integrated with a portable personal computing device (hereinafter "a PHHCD"). PHHM uses the PHHCD processor to control and analyze the signals received from the signal acquisition device. The present invention also relates to a signal acquisition device, adapted to be integrated with such PHHCD. The present invention further relates to systems for operating the PHHM and for manipulating the signals acquired by the signal acquisition device. The present invention further relates to a system for analyzing, storing and transmitting the signals acquired by the PHHCD over the Internet, or for regulating the uses in which data derived from these signals can be placed. BACKGROUND OF THE INVENTION
    [0002] Cell phones (also known as mobile phones) are a part of daily life. In the developed world, the vast majority of adults own a cell phone. The use of cell phones is also becoming very prevalent in developing countries as it allows these countries to develop a communications system without the need to install cabling. There are several proposals for the use of cell phones in health care. However, all these proposals have shortcomings.
    [0003] Leslie, I. et al., "Mobile Communications for medical care", Final Report, April 21, 2011, reports on a large study, by the University of Cambridge, that identified the crucial contribution that cell phone networks make. they will do health care in developed, low-income and emerging countries by transferring "vital signs" and other data from local measuring devices to a central computer for data collection and processing. It identified two separate industrial communities - those that produce cell phones and those that produce medical devices.
    [0004] Ladeira D. et al., "Strategic Applications Agenda Version 3", Working Group on Leading Edge Applications, January 2010, www.emobility.eu.org, which is an e-mobility study, which considered the broad networked healthcare implications and stated: "Smart phones can automatically and wirelessly collect measurement results from measurement devices and fully transfer the collected data to the physician for further analysis."
    [0005] "Healthcare unwired - new business models delivering care anywhere", PricewaterhouseCoopers' Health Research Institute, September 2010, is a study that addresses the opportunity presented by broad access to communications, but from the perspective of the medical profession and its impact on the medical business template.
    [0006] In a 2009 review, Apple Company identified a growing demand for the use of its iPhone® as part of a communications chain from medical devices to practitioners and others (see htpp://medicalconnectivity.com/2009/03 /19/apple-targets- health-care-with-iphone-30-os/).
    [0007] These records are based on the use of existing medical devices and existing cell phone technology, and therefore require the presence of both a medical device industry and a cell phone industry. It is an objective of the present invention to provide data collection related to health, without the need for both these industries.
    [0008] Tablet computers and portable personal computers are also getting small enough to be used as PHHCDs. Many of these devices also include communications features such as WiFi or wireless phone connectivity.
    [0009] Personal Digital Auxiliary Devices ("PDAs") are also now well known and include a processor, to allow a user to store and retrieve personal data. THE PRESENT INVENTION
    [00010] According to a first aspect of the present invention, there is provided a personal portable monitor (hereinafter "a PHHM") comprising a signal acquisition device for acquiring signals, which can be used to derive a measure of a parameter. related to user health, the signal acquisition device being integrated with a personal handheld computing device (hereinafter "a PHHCD").
    [00011] The PHHM of the present invention should be of a size and weight such that it can be easily manipulated by a normal adult, using one hand to hold the PHHM and the other hand to input or retrieve data. Preferably, the PHHCD includes communications features such as WiFi or wireless phone connectivity.
    [00012] By "integrated" it is meant that the signal acquisition device and the PHHCD form a single physical unit, in which the signal acquisition device and the PHHCD are kept in a fixed relationship, when either of them is moved . All electrical connections are provided within the PHHM.
    [00013] The acquired signals can be analog or digital, and, if analog, can be converted to digital form for subsequent analysis by the PHHCD processor, or for analysis by a remote data processing facility, with which the PHHCD communicates by use of the Internet or other data communication means.
    [00014] The PHHCD with which the signal acquisition device is integrated can be a cell phone, a tablet computer, a PDA or any other computing device, which can be easily manipulated by a normal adult, using one hand to hold the PHHM and the other hand to input or retrieve data.
    [00015] The present invention joins medical technology with PHHCD technology by combining proven technological principles with a new implementation, to create a PHHM, which allows its user to acquire personal health data measurements just by using PHHM. If desired, the user can communicate these measures to third parties.
    [00016] The use of the PHHM of the invention is a significant improvement over the use of the systems described in the studies referred to above, because the signal acquisition device is integrated with the PHHCD. Since the signal acquisition device must be small enough to be integrated with the PHHCD, without reducing its portability and being able to make use of the PHHCD infrastructure, such as its display and its battery, it will be significantly cheaper than that many of the well-known medical devices, which are too expensive for most users in low-income or emerging countries, will even convince those in developed countries. The signal acquisition device exploits microelectronic technology to reduce size and cost to a level where the signal acquisition device, integrated with a PHHCD, can become ubiquitous and personal to the user.
    [00017] Preferably, the signal acquisition device is adapted to acquire signals while in contact with or in close proximity to one or more parts of the user's body. In particular, the signal acquisition device can be adapted to acquire signals as long as, at least in part, it is in contact with: - one or more digital elements of the user, especially one or more fingers; - the skin close to the carotid artery; - the user's chest, advantageously close to the heart; and/or - the inside of a user's ear or mouth.
    [00018] The signal acquisition device includes one or more sensors to acquire signals, which can be used to derive a measure of a parameter, which is useful in relation to personal health. Preferably, the one or more sensors is(are) to acquire signals relating to blood pressure, pulse waveform, blood pressure waveform, temperature, blood oxygen partial pressure, electrocardiogram, heart rate and/or frequency respiratory. The signal acquisition device may include sensors for signal acquisition, from which measurements of one or more of the parameters mentioned above may be derived. The signal acquisition device preferably includes one or more sensors for acquiring signals, of which blood pressure measurements, using, for example, one or more of sphingmomanometry, photoplethysmography and pulse wave velocity measurement, may be derivatives.
    [00019] The PHHM of the present invention may include one or more of the following sensors and means. Particularly preferred combinations of these sensors and means are referred to below. Temperature sensor
    [00020] The signal acquisition device may include a temperature sensor, to acquire signals from which a measure of local body temperature (i.e., the temperature close to where the sensor is applied to the body) can be derived by the processor of the PHHCD. Advantageously, the signal acquisition device also includes a sensor for acquiring signals from which a measure of ambient temperature can be derived by the processor. This can be the same sensor as the one used in conjunction with the local temperature measurement, or it can be a separate sensor. Preferably, the processor is adapted to derive the user's core body temperature from the signals acquired by the temperature sensor.
    [00021] As is well known, the temperature of a surface can be estimated by measuring the thermal radiation it emits. For typical body temperatures, radiation is concentrated at wavelengths in the far infrared region. They can be detected by a bolometer, in which a target is heated by incident radiation and its temperature measured, directly by detecting the variation in its resistance or indirectly using a thermocouple, thermistor or other similar device. The field of view can be defined by a lens or window. The temperature sensor can be adapted to receive radiation from the inner ear or temporal artery in the forehead, as in existing medical devices using this technique.
    [00022] The temperature sensor is preferably positioned so that it is able to detect the temperature of the user's ear, whether or not the user is making a phone call. Alternatively, the temperature sensor can be positioned so that it is possible to take measurements of the surface temperature of the body part, at which any other measurement made by the PHHCD, such as a blood pressure measurement, will be taken.
    [00023] Alternatively, the temperature sensor can be located so that the user can guide their direction, by manipulating the PHHCD so that it is possible to monitor the temperature of the body part or other selected item, for example, an item of clothing from the user. The PHHCD processor can, in this case, be adapted to derive a signal indicative of ambient temperature, and/or provide instructions to the user, to guide the PHHM so that the signals indicative of body temperature and ambient temperature are obtained.
    [00024] Alternatively, the temperature sensor can be located on an arm, which can be placed in contact with one of the user's fingers or inserted into the user's ear or mouth. The arm can be fixed in position on the signal acquisition device, or it can be movable between an extended and a retracted position, so that the arm can be retracted when not in use. The arm can be pivoting or sliding between its extended and retracted positions.
    [00025] The signal acquisition device can include more than one temperature sensor, to monitor temperature at different locations.
    [00026] The temperature sensor can be used to measure the temperature of other items, for example in food, home heating systems or wine. electrical sensor
    [00027] The heart is triggered by electrical signals, which can be detected on the skin, which is the basis of the electrocardiogram (ECG). A simple version of this can detect the time at which the electrical signal that starts a heartbeat occurs by measuring the potential difference between two separate parts of the body. With proper electronic processing, the time of occurrence of each initiation signal can be measured within a few milliseconds.
    [00028] The signal acquisition device can include an electrical sensor, comprising two electrodes, which are electrically isolated from each other, but which can be brought into contact by two different parts of a user's body. Preferably, the two electrodes can be brought into contact with one finger on each of the user's hands. Preferably, one of the electrodes of the electrical sensor is associated with the blood flow occlusion means button, pad or strip (see below). The other electrode will be located in a separate part of the PHHM. This other electrode can be associated with a lever, if present, which is used for manual inflation of a cushion (see below). Preferably, the pad is constructed with a surface that provides a good electrical connection, such as a micropyramid array.
    [00029] Preferably, the signal, which is acquired by the electrical sensor, is a measure of the potential difference between the two electrodes, which is related to the potential difference between two different body parts. Preferably, the PHHCD processor is adapted to amplify the signals from the electrical sensor, and, if desired, filter the signals before, during or after amplification. An amplified and filtered signal produced by the processor will generally have the form shown in Figure 1 in the accompanying drawings, where the x axis represents time and the y axis represents potential difference. The arrows in Figure 1 indicate the time at which the electrical signal stimulates the heart to start systole. Blood flow occlusion means
    [00030] The signal acquisition device may comprise a blood flow occlusion means, to restrict or completely block blood flow through a part of a user's body, and a pressure sensor to determine the pressure applied by or in the medium. of blood flow occlusion. The conventional blood flow occlusion means is an inflatable cuff, which encircles the body part.
    [00031] The signal acquisition device preferably includes one of the blood flow occlusion means which are described below: a button, a fluid-filled pad; and a strip. Any of these can be used by compressing them on a body part, such as a toe or a finger, preferably a finger, when arterial blood flow through the body part is affected by pressure exerted on just one. side of the corporeal part, or vice versa.
    [00032] The degree of occlusion can be detected by an oscillometric method or by analyzing the signals from a blood photosensor described below. Button
    [00033] The blood flow occlusion means may comprise a button, which is compressed in the body part. Preferably, the button is a region of a plate whose region can move independently of the rest of the plate and is connected to a force sensor. The force sensor is adapted to measure the force applied to the button, but to minimize the distance the button can move. Typically, the plate is 10 mm by 20 mm, with a circular button typically 5 mm in diameter or a non-circular button of similar area. Preferably, the distance over which the button moves, when subjected to the force of the body part, is not more than 0.1 mm.
    [00034] Compression of the button on the body part creates pressure within it. The body part, in contact with the button, is pushed into the button with a force approximately equal to the pressure inside the body part, multiplied by the area of the button. By measuring strength, the PHHM can make an accurate estimate of the pressure within the body.
    [00035] The signal acquisition device may include several buttons, each of which is connected to a separate force sensor. Cushion filled with fluid
    [00036] The blood flow occlusion means may comprise a fluid-filled pad, in which one side of a user's bodily part, in particular a digital element, preferably a finger, can be compressed to occlude the blood flow through the body part, in a pressure sensor to provide a signal indicative of pressure in the cushion. Preferably, the pad is located in a notch in the PHHM. In use, pressure can be applied to the pillow by compressing the body part into the pillow or by compressing the pillow into the body part.
    [00037] If the cushion is filled with air, it may be necessary to provide a means to prevent excess pressure from occurring in the cushion. This can arise, for example, if the device is left in a warm place, and the heat causes the pressure to build up excessively. The overpressure prevention means preferably includes a valve that opens to release gas from the cushion to the atmosphere at a predetermined pressure, which is the maximum allowable pressure of the cushion (approximately around 40 kPa - 300 mm Hg ), and a pump to replenish the gas that has been released. The pump can comprise a piston and a cylinder, or it can comprise a diaphragm and a chamber, and the piston or diaphragm can be operable by user action or by electrical energy. Preferably, the PHHM has a sliding or hinged cover, on which the signal acquisition device is arranged so that when opening the cover it can be used, the cover compresses the piston or diaphragm to create a pressure. enough to re-inflate the cushion. Preferably, the pump has two valves: a one-way valve, which allows gas to enter the cushion; and a valve for opening to release the pump gas to atmosphere at a predetermined pressure, which is the minimum operating pressure of the cushion (typically around 6.7 kPa - 50 mm Hg).
    [00038] It is advantageous that the volume of gas present in the cushion is maximized, to maximize the sensitivity of the detection of changes in pressure. If a one-way valve is used, it should preferably be located close to the cushion and pressure sensor.
    [00039] Another benefit of incorporating this means of deterrence is that the device continues to operate even if a slow leak develops. This will increase device reliability. Strip
    [00040] In another alternative, the blood flow occlusion means may comprise a strip, in which one side of a user's bodily part, in particular a digital element, preferably a finger, may be compressed to occlude the blood flow through the body, and a force sensor to provide a signal indicative of the pressure exerted on the strap.
    [00041] Preferably, the strip is located in a notch in the PHHM. In use, pressure can be applied to the strip by pressing the corporeal part into the strip or by compressing the strip into the corporeal part.
    [00042] The strip can be extensible or not.
    [00043] When the strap is not extensible, it can be securely mounted on each end by a notch in the PHHM. In that arrangement, the pressure sensor is adapted to measure the force applied to the strap assemblies.
    [00044] Alternatively, an inextensible strap can be mounted on a mechanical shaft, on one side of a notch, and securely mounted on the other side of the notch. In this arrangement, the pressure exerted on the strip can be measured by measuring the extent to which the strip has been wound around the mechanical axis. Unwinding can be resisted by a torque spring on the mechanical shaft or a linear spring.
    [00045] In another alternative, an inextensible strip can be mounted at each of its ends on a mechanical shaft, and the mechanical shafts are located at each end of a notch in the PHHM. In this arrangement, the pressure exerted on the strip can be measured by measuring the extent to which the strip has been wound around each mechanical axis, or by measuring a physical property of the strip, such as its electrical resistance.
    [00046] When the strap is extendable, it can be securely mounted on each end by a notch in the PHHM. In such an arrangement, the pressure sensor can be adapted to measure the increase in strip length or tension in the strip, or measure a physical property of the strip, such as its electrical resistance, to provide the signal relative to the pressure applied to the strip.
    [00047] When a strip is used, it is preferred that the PHHM include a means to provide a signal indicative of the diameter of the body part, which is in contact with the strip, so that the pressure measurement can be made more accurate. The means may be a compact keyboard or a touch screen, advantageously the compact keyboard or normal touch screen of the PHHCD, whereby a user can input the diameter measured by the user, for example using any convenient means such as a tape measure or a series of graduated cuts provided in a separate standard measure, or provided in the PHHCD.
    [00048] However, it is preferred that the medium is associated with the strip itself and provides the signal without user input. For example, the strip may include one or more optical fibers embedded therein, a light source at one end of the one or more optical fibers, for injecting light into the optical fiber(s), and a light detector at the other end of the optical fiber(s). optical fibers, to detect the light reaching the detector, and a means to determine the attenuation of light as it passes through the optical fibers, the degree of attenuation being relative to the curvature of the strip, which is, in turn, relative to the diameter. Alternatively, the strip may comprise two layers, and the signal acquisition device includes means for measuring the length of each layer, the relative lengths of the two layers being related to diameter. In another alternative, the signal acquisition device may include a means, such as a proximity detector, for providing a signal indicative of the distance between the bottom of the notch and the point closest to the strip to the bottom of the notch, and the processor is adapted to calculate the diameter of the body part, based on the sign and the length of the strip. Blood photosensor for photoplethysmography (PPG)
    [00049] Pulse oximeters using PPG have been on the market since the 1980s. They are used to estimate the degree of oxygenation in arterial blood. Red and infrared light are transmitted to a bodily part. Infrared light is more intensely absorbed by oxygenated blood than by non-oxygenated blood; red light is more intensely absorbed by unoxygenated blood than by oxygenated blood. The variation in infrared light absorption during systole is a measure of the amount of oxygenated blood. The red light absorption level, between systoles, is a measure of the total amount of blood being illuminated and is used for calibration.
    [00050] Preferably, the signal acquisition device includes a PPG sensor. This one uses one or more photosensors. The photosensor(s) can be arranged for measurement of transmission or dispersion. In transmission mode, the photosensor comprises one or more photoemitters arranged to transmit light through the bodily part, and one or more photodetectors arranged to detect light transmitted from the photoemitter(s) by that part. In scatter mode, the photosensor comprises one or more photoemitters arranged to transmit light towards the body part and one or more photodetectors arranged to detect light from the photoemitter(s) scattered throughout the body part. Preferably, in scatter mode, the photodetector(s) is(are) arranged in close proximity to the photoemitter(s).
    [00051] Preferably, in any case, the photosensor(s) is (are) adapted to emit and detect light in two or more wavelengths. There may be a single, multiplexed photoemitter adapted to emit light of two different selected wavelengths, or at least two photoemitters, each of which is adapted to emit light of a different selected wavelength. In any of the alternatives of the photoemitter(s), in one alternative, there is a multiplexed photodetector, which can detect light at selected wavelengths. In another alternative, there are two or more photodetectors, each of which is adapted to detect light of a different selected wavelength.
    [00052] Preferably, one of the wavelengths is selected so that the light is absorbed more intensely by oxygenated blood than by deoxygenated blood. A suitable wavelength is 940 nm. Another wavelength is selected so that light is absorbed more intensely by deoxygenated blood than by oxygenated blood. A suitable wavelength is 660 nm.
    [00053] Preferably, the signal acquisition device is adapted to acquire a signal from the photodetector(s) when no light is emitted from the photoemitter(s). This provides additional calibration of the signals obtained on the first and, if used, on the second wavelength.
    [00054] Figure 2 shows, in the attached drawings, the variation in oxygenated blood signal (top line), deoxygenated blood signal (middle line) and ambient light signal (bottom line).
    [00055] The blood photosensor can be further adapted to measure the concentration of analytes in the blood, such as glucose, alcohol, hemoglobin, creatinine, cholesterol and stimulants, or other medications, including illegal or otherwise prohibited substances. These are difficult to measure if the analyzer's absorption spectrum is similar to that of other materials in the blood. The signal acquisition device can be designed to use one or more of the techniques described below to increase the sensitivity and selectivity of absorption spectroscopy.
    [00056] The first technique is to use differential absorption. A beam of light is transmitted to a bodily part, and the transmitted or scattered light is split between two monitoring cells. One (the reference cell) contains a mixture of chemicals typically present in sufficient proportions in the blood, excluding the analyte of interest. In practice, this can only contain water. The other (the sample cell) contains the same mixture and the analyte. Alternatively, the reference cell can be omitted, and the sample cell filled with only the analyte. Alternatively, if the analyte can be gaseous under ambient conditions, the light beam can pass through a single sample cell, containing the analyte in gaseous form, and the pressure in that cell is modulated.
    [00057] The intensity of the light beam can be measured under various conditions: after passing through the reference cell, and separately passing through the sample cell, in each case without the body part present, and, similarly, after passing through each cell with the body part present. Alternatively, the intensity of the light beam can be measured either when it has passed through the cell or when it has not, again with the body part present and not. In another alternative, the intensity can be measured as a function of the pressure in the cell, with and without the body part present.
    [00058] The intensity of the light beam can be modulated, for example, by switching, to allow the measurement system to compensate for the ambient light. The light beam has a broad optical spectrum, selected to maximize discrimination between the analyte and other chemicals present, while also allowing low-cost technology to be employed. For example, if the analyzer is glucose, it may be in the region close to the infrared.
    [00059] In each case, the difference between the intensity when the light beam has passed through the reference cell and that through the sample cell is a measure of the degree of absorption by the analyser into the body part. To further improve the selectivity for the concentration of the analyte in the blood, the PPG signal can be used to identify the time at which the artery dilates due to systole. The variation in absorption at this point is only a consequence of the additional amount of blood in the body part. The volume of this additional blood is also estimated from the PPG signal. Acoustic sensor
    [00060] The PHHM can include an acoustic sensor, to acquire the signals related to the sounds produced by the heartbeat. The acoustic sensor can be a separate microphone, a geophone or a vibration sensor, or it can be the microphone provided in a usual cell phone or tablet-type computer for speech reception, or it can be the force or pressure sensor used to measure pressure in the body part during arterial occlusion. Preferably, the PHHM processor is adapted to process the signals acquired by the acoustic sensor to determine the time at which the heart beats.
    [00061] Figure 3 shows, in the attached drawings, a typical waveform of the beating "lub-dub" of the heart, which will be acquired by the acoustic sensor. Two successive pulses are shown. The signal consists of an audio signal within an amplitude envelope. Motion sensor
    [00062] The PHHM may also include a motion sensor, which is adapted to detect the location of the user's body part in which the signal acquisition device is located. Preferably, the PHHM processor is adapted to correlate the signal from the motion sensor with the signal from a pressure sensor to allow calibration of the blood pressure measurement. Preferably, the PHHM processor is adapted to issue instructions, audibly or visibly, to the user, to move the bodily part so that calibration can take place. The motion sensor can be an existing component of the PHHCD. It can detect inertial forces due to PHHCD acceleration or pressure variations with altitude. ultrasonic sensor
    [00063] The signal acquisition device may include an ultrasonic sensor to image the cross-section of the artery and/or use Doppler interferometry to estimate the velocity of blood flow within the artery. Said ultrasonic sensor may consist of a set of individual elements that form an array. Means of inputting personal data
    [00064] Preferably, the PHHM includes a means of inputting personal data and is adapted to store other personal data. The personal data input means is preferably a compact keyboard or a touch screen, advantageously the compact keyboard or normal touch screen of the PHHCD. Data, which may be entered in this way, may include, but are not limited to: height, weight, waist circumference, finger diameter, and age. Other sensors and means
    [00065] The PHHM can further include a means to apply electrical signals to the user's body, and detect the signals produced in response to these signals, for example, to measure body properties such as the body mass index.
    [00066] The PHHM may include a sensor adapted to acquire signals from which the user's identity can be derived, such as taking a user's fingerprint. This makes it possible to ensure that derived measures relating to the user's health can be directly associated with the user. This identity sensor can be associated with the pad of a blood flow occlusion means, or it can be associated with an electrode of an electrical sensor. It is possible to locate the identity sensor in such a way that it is almost impossible for the measured medical indicators to be from anyone other than the identified user. DATA ANALYSIS
    [00067] The sensors and means described above can be used in various combinations to allow the acquisition of various health-related data. The PHHM may include one or more of temperature sensor, electrical sensor, blood flow occlusion means, blood photodetector for PPG, acoustic sensor, motion sensor, ultrasonic sensor, and preferably includes at least the first four of these . The preferred combinations of sensors and media are shown in the table below, along with indications of health-related data, which can be derived using these combinations. However, it will be clear to those skilled in the art that other combinations can be used to provide other health related data, and the present invention is not to be limited to the combinations shown in the table below.



    [00068] The table does not refer to the analysis of data derived from the possible extension of the optical sensor, to measure the concentration of an analyte in the blood.
    [00069] Algorithms relating to the combination of signals from any or all of the sensors and media contained in the PHHM, and from other sensors, which may be part of the PHHCD, can be used to convert the acquired signals into relevant health-related data, or improve the accuracy of deduced medical indicators ("vital signs"), such as systolic and diastolic blood pressures. Other medical indicators, which are less well known but which can be recognized by medical specialists, such as arterial wall stiffness and pulse arrhythmia, can also be extracted. Any or all of these models can be coded as software and can be loaded into PHHM or a remote computer for signal processing.
    [00070] Preferably, the PHHM processor is adapted to provide audible or visual instructions to the user, to allow him to optimally use the PHHM. In that case, it is preferred that the processor be adapted so that the instructions are interactive and based on signals received from the signal acquisition device, which can be used to determine whether the signal acquisition device is in the best position or is being used correctly.
    [00071] It is preferred that the processor be adapted to take multiple measurements and correlate all these measurements to provide a better indication of the health data. A possible arrangement by which sensor data is analyzed is described after the table. body temperature
    [00072] The accuracy of body temperature estimation can be improved by adapting the PHHCD processor to provide audible or visual feedback to instruct the user to move the PHHM in order to generate a maximum temperature reading, for example, when the PHHM is placed on the user's ear and is moved to ensure the sensor is aimed at the warmest location.
    [00073] Preferably, the temperature sensor is positioned on the PHHM, so that this is able to cover the body part whose temperature is being measured, such as the ear. In this case, in use, the temperature can rise towards the core temperature, because deviations are eliminated by the presence of the PHHM. The temperature sensor can be placed on or combined with a speaker, or other device used to reproduce sound on the PHHCD.
    [00074] Preferably, the processor is adapted to record the measured temperature over a period of several seconds and use a mathematical model to extrapolate to a predicted equilibrium temperature.
    [00075] The PHHM processor can be adapted to analyze the temperature sensor signals to provide an estimate of the user's core body temperature. The processor can be further adapted to conduct analysis, to identify trends in core temperature and other information derived from diagnostic value. pulse frequency
    [00076] The time of each pulse can be determined from the electrical signal, which indicates the onset of systole, and also from the arrival time of the systolic pulse in the body part, in which the device is compressed, indicated by the pressure on the sensor of pressure or force, in the occlusion medium, and by the absorption peak detected by the optical sensor and/or by the acoustic sensor, if present(s).
    [00077] The average pulse frequency most compatible with all data from each of these sensors is determined by means of a mathematical optimization algorithm, with which the PHHCD processor is adapted to operate. This can be a simple least squares difference calculation, with weighting, or you can use a Bayesian estimator or other optimization technique to determine the most likely estimate. pulse arrhythmia
    [00078] Arrhythmia is a term used to refer to the variation in the interval between pulses. Models of these variations are valuable diagnostic tools.
    [00079] Variations can be obtained from the same data used to determine the average pulse frequency, again optionally using a mathematical optimization algorithm. Blood pressure
    [00080] Blood pressure can be estimated by combining data from four different types of evidence: pulse wave velocity, pulse volume, sphygmomanometry and pulse rate. Sphygmomanometry is itself derived from two different measurements, the high-frequency signals from the pressure sensor or one or more photosensors. External data such as the user's height, weight, age and gender can also be exploited. There are thus five separate measurements and several data fractions, which can be combined using a mathematical optimization algorithm, such as a Bayesian estimator, to obtain the safest estimate of blood pressure.
    [00081] The resulting values are the systolic and diastolic blood pressures at the location of the body part where the measurement was taken. Other diagnostic information can be extracted from the signals using other mathematical models. For example, the analysis can calculate blood pressure at another point on the body, such as the arm, to allow direct comparison with measurements by a cuff-based sphygmomanometer. It can also calculate pressure in the aorta as well as arterial stiffness.
    [00082] Optionally, the PHHM can include another temperature sensor, to detect the artery to be tested.
    [00083] All blood pressure measurements are described below. pulse wave velocity
    [00084] Pulse Wave Velocity (PWV) can be derived from Pulse Wave Transition Time (PWTT).
    [00085] The use of PWV to estimate blood pressure (BP) is described in detail by Padilla et al. (Padilla J. et al., "Pulse Wave Velocity and digital volume pulse as indirect estimators of blood pressure: a pilot study on healthy volunteers", Cardiovasc. Eng. (2009) 9:104 - 112), which in turn makes reference to earlier work on a similar subject from 1995, and its specific use for estimating bP in 2000. The technique is described in US Patent 5,865,755, dated February 2, 1999. It is based on the observation that the speed at which a pulse of blood travels along the arteries is a function of arterial blood pressure.
    [00086] Preferably, the PHHM processor is adapted to derive a PWV estimate from the signals obtained from the electrical sensor and the PPG sensor. The processor is adapted to process the electrical sensor signal to provide an indication of the time at which systole (the heartbeat) is initiated and to process the photosensor signal to determine the time of peak occurrence in the oxygenated signal, which indicates the time at which the pulse reaches the measurement point. The interval between these is a measure of the time it takes for the pulse to move from the heart to the measurement point (the PWTT). The processor is adapted to determine BP in relation to this interval, which is typically 300 ms for wrist or hand tip measurements.
    [00087] Preferably, the processor is adapted to make use of two other pieces of information to estimate the PWV: the time delay between the electrical start signal and the start of systole by the heart; and the length of the path between the heart and the measurement point.
    [00088] Preferably, the processor is adapted to analyze the acoustic signal to extract the envelope (analogous to detection in radio signals) and use an automatically adjusted threshold to identify the point, which indicates the onset of systole. In practice, this may be a defined fraction of the background and peak variation, as shown in Figure 4 of the attached drawings, where the vertical arrows indicate the time at which the heart responds to an electrical signal of physiological onset, and starts to systole. This is typically a few tens of milliseconds after the electrical start signal. Alternatively, the processor is adapted to fit a curve to the waveform to generate a more meaningful estimate.
    [00089] Alternatively, time delay can be estimated by measuring the PWTT in two different parts of the body, such as the carotid artery and the finger. The time delay can then be determined by knowing the typical ratio of path lengths from the heart to the two different parts of the body.
    [00090] Preferably, the PHHM is adapted to store the time delay in a non-volatile memory. It can be automatically stored when measured or entered into memory by user input using a compact keyboard or touch screen, advantageously the compact keyboard or normal touch screen of the PHHCD.
    [00091] Preferably, the PHHM is adapted to store in a non-volatile memory a value relative to the length of the path between the heart and the measurement point. It can be entered into memory by user input using a compact keyboard or touch screen. The value entered can be an exact measure of length, or it can be a value that is approximately proportional to the actual length, such as the user's height. pulse volume
    [00092] Pulse volume can be derived from the blood photosensor (PPG). The use of PPG to estimate BP was registered by XF Teng and YT Zhang in the IEEE EMBS, Cancun, Mexico, September 17 - 21, 2003. The basic technique was the subject of US patent 5,140,990, dated August 25, 1992. The change in infrared absorption during systole is a measure of the change in volume of the artery being illuminated, which is relative to the pressure within the artery.
    [00093] Other data can be derived from the analysis of the shape of the absorption peak during systole, such as the analysis of the total area under the peak.
    [00094] Preferably, for the signal for oxygenated blood, the PHHM processor is adapted to derive blood flow properties, such as the relative amplitude and the synchronization of the reflected and direct pressure wave of the curve shape, such as the area under the peak, its width at half height and the height and length of the shoulder. Optionally, the PHHM processor can be adapted to calculate these ratios to reduce the effect of variations in lighting and location relative to the body part. These reasons can be used to characterize the properties of blood flow.
    [00095] The PHHM processor is preferably adapted to analyze the PPG sensor signals, to provide a direct estimate of systolic and diastolic blood pressures at the measurement point. Sphygmomanometry (arterial occlusion)
    [00096] Sphygmomanometry is a mature technique to measure BP, which has been used for over 100 years. Variable external pressure is applied with a cuff around the body part, inside which an artery runs. Pressure reduces the cross-section of the artery and limits blood flow during systole.
    [00097] Sphygmomanometry is conventionally conducted with a cuff, which surrounds the body part and is inflated to a pressure at which all blood flow is stopped; the pressure is then released slowly. Systolic BP is measured by determining the lowest pressure that completely impedes flow. Diastolic BP is measured by determining the highest pressure that does not cause any occlusion. Flow is traditionally detected by a skilled practitioner, using a stethoscope to hear the sounds of blood flowing (Korotkoff sounds).
    [00098] Automatic sphygmomanometers detect the flow by reducing fluctuations in pressure in the cuff caused by the flow (oscillometric method, see, for example, Freescale application note AN1571, "Digital Blood Pressure Meter") or by optical monitoring of small skin movements. The magnitude of these fluctuations is an indicator of the degree of occlusion. More recently, PPG has been used by combining sphygmomanometry with pulse volume measurement (see Reisner et al, "Utility of the Photoplethysmogram in Circulatory Monitoring", Anesthesiology 2008; 108:950 - 8).
    [00099] The signal acquisition device can use any of the three occlusion means described above: a fluid-filled pad, a strip or a button. It uses both pressure fluctuations and pulse volume measurement to determine systolic and diastolic pressures.
    [000100] Unlike conventional sphygmomanometry, flow can be detected over a range of pressures, in any order, and the data fitted to a known mathematical equation. It is preferred that the processor be adapted to issue audible or visual instructions to the user, to vary the force applied to the body part, to cover a sufficiently wide range of pressures to provide a good fit to the mathematical equation. For example, if the user has not compressed firmly enough on the above button, strip or cushion to completely occlude a blood vessel during systole, the device can be programmed to issue an instruction to the user to compress more firmly in the middle of occlusion (or vice versa) so that the required data can be acquired.
    [000101] This capability allows the pressure, applied to the occlusion medium, to be seemingly random. In conducting blood pressure monitoring, the user can vary the pressure applied to the above mentioned button, pad or strap in a random manner. However, the blood flow sensor data can be correlated with the signal from the button, pad or strap pressure sensor to adjust the measured data to a known theoretical relationship between flow and pressure (see, for example, the model shown on page 954 of Reisner ("Utility of the Photoplethysmogram in Circulatory Monitoring"), Anesthesiology 2008; 108:950 - 8)). pulse frequency
    [000102] Pulse rate can be measured separately and can be used as an indicator of blood pressure. Al Jaafreh ("New model to estimate mean blood pressure by hear rate with stroke volume changing influence", Proc 20th IEEE EMBS Annual Intnl Conf 2006), concludes that: "The relationship between heart rate (HR) and mean blood pressure ( MBP) is non-linear". The article then shows how to allow the beat volume to be partially compensated for this non-linearity. Beat volume is estimated separately (see below) and personal data can also be used. blood oxygen
    [000103] The blood photosensor can use PPG to estimate blood oxygen levels. At least four variables can be derived from the absorption measured at two wavelengths. These are the amplitude of the signal detected at each wavelength in systole and between systoles. The arrow in Figure 2 shows one of the values that can be derived from these, the height of the peak corresponding to the change in signal of oxygenated blood in systole. It has been established that these four values can be analyzed to estimate blood oxygenation (see, for example, Azmal et al., "Continuous Measurement of Oxygen Saturation Level plant Photoplethysmography signal", Intl. Conf. on Biomedical and Pharmaceutical Engineering 2006, 504 - 7). pulse wave velocity
    [000104] The pulse wave transition time can be measured as shown above, and converted to a pulse wave velocity estimate. This information is of direct diagnostic value to a skilled practitioner, especially when considered with all other data obtainable from the signal acquisition device of the present invention. respiratory cycle
    [000105] The state of the breath cycle can be detected from several of the data sets measurable by the present invention: - pulse rate (measured by electrical sensor and blood photosensor, see below); - mean blood pressure (see above); and - systolic pulse amplitude (measured by PPG, see above).
    [000106] The results of all these measurements can be combined by using a mathematical optimization algorithm, such as a Bayesian estimator, to obtain the safest description of the amplitude and phase of the respiratory cycle. Blood flow/Heartbeat volume
    [000107] The volume pumped by the heart in each pulse is conventionally measured using an ultrasonic scan. The cross-sectional area of the aorta is estimated from the Doppler shift image and flow rate. This is a mature and inexpensive technique, but it is only available in a doctor's office.
    [000108] Before ultrasound was readily available, a convenient and almost non-invasive technique was to estimate the time it takes for blood to circulate throughout the body. This is related to the pulse rate and the volume pumped in each pulse. The technique used a strong-tasting but innocuous chemical that was injected into a vein in the arm, and the time measured before it reached the patient's tongue and could be tasted.
    [000109] The present invention provides that a similar measure is made by disturbance of the respiratory cycle. The PHHCD can be adapted to instruct the user to hold their breath. The oxygen level in the lungs starts to drop and the blood oxygenation in the lungs drops with it. Once this blood reaches the point in the body at which measurements are being taken, the oxygen level in the blood will be observed to drop. The time interval, when combined with the data considered or entered as for the path length, is a measure of flow velocity. The PHHCD then instructs the user to start breathing again, and the time that passes before the blood oxygen level starts to rise again can also be measured. REMOTE DATA PROCESSING
    [000110] PHHM is capable of taking and displaying measurements of any or any combinations or all of the "vital signs" listed above, in any external data processing. Additional aspects and improved accuracy can be provided by external data processing, using the communications capability of the PHHCD, for connection to the Internet, a cellular telephone network or other means of communications.
    [000111] Preferably, each PHHM according to the invention has an electronically readable, unalterable, unique identifier. This can be provided during manufacturing or testing. Furthermore, each PHHM preferably includes a set of circuitry to encode the measured data in a way that is unique to that device.
    [000112] In an embodiment of the present invention, the PHHCD reads the unique identifier when the PHHM is first used and transmits that identifier to remote secure data service (RSDS) via the Internet. RSDS downloads to the PHHCD the necessary software, calibration data and decode key to extract the data from PHHM. This is a safer way to ensure proper calibration of the signal acquisition device and minimizes the time required for installation and final testing of the PHHM on the PHHCD. The PHHCD is preferably further programmed to communicate the measured data directly to the user, for example via a visual monitor or audibly. Preferably, communication is via a visual monitor. If desired, the processor can be programmed so that the monitor shows not only the measured parameter(s), but also the trends of the measured parameter(s).
    [000113] Optionally, the software can be time limited, requiring the user to revalidate it with RSDS after a fixed period of time. Optionally, the user may need to pay a license fee for part or all of the capacity to be enabled.
    [000114] Alternatively, the description key and calibration data can be retained by RSDS. The PHHCD transmits the raw coded data from the PHHM to the RSDS for analysis. RSDS then returns the calibrated, decoded data for further processing and display to the user.
    [000115] RSDS can conduct further processing of the measured data to obtain greater accuracy, or derive other diagnostic or indicative data. This data can be relayed to the PHHCD for display to the user.
    [000116] The PHHCD can also be programmed by RSDS to transmit the acquired signals or the derived measurements to a remote location, for example, a user computer system, clinic, healthcare provider or insurance company, in which the acquired signals or measurements can be processed remotely, for example, to provide a more accurate analysis, or the analysis results to be interpreted automatically or by a qualified physician. If the programmer is so programmed, it can also be programmed to receive the results of this analysis and display these results to the user as described above.
    [000117] PHHCD can also be programmed by RSDS to allow third party applications (commonly known as "apps") to access PHHM data. Such permission may be subject to payment of a license fee or the app having been endorsed by the relevant regulatory authorities.
    [000118] The PHHCD can also be programmed to provide information relating to one or more derived measures, such as normal ranges or recommendations for action.
    [000119] RSDS can provide a service to store many measurements of a PHHM and analyze trends and other derived information for the user. This can be linked to an automatic alert service in case of any significant variations in the data. In addition, signals or measurements can be protected anonymity and pooled from groups or all of the PHHMs of the invention so that they can be used for research purposes. PHYSICAL CONSTRUCTION
    [000120] Several different sensors and means, like the ones mentioned above, can be incorporated in the PHHM. They can be incorporated individually or in any combination of two more sensors. For example, a combination of a sensor, to measure the pressure applied by a pad, strip or button, or applied to a pad, strip or button, a photosensor to measure blood flow in a body part, to which pressure is applied , and an electrical sensor, for measuring a pulse rate, is particularly useful for providing more accurate data for determining blood pressure. Preferably, the PHHM integrates one or more Application Specific Integrated Circuits (ASIC), one or more Micro-Engineered Measurement Systems (MEMS) and/or photoemitters, and/or photodetectors. They can all be integrated as separate silicon devices in a single package, or preferably some or all of them can be incorporated into one or more silicon devices. This integration will bring many benefits, including reduced cost, increased reliability, reduced size, and reduced power and mass consumption.
    [000121] Preferably, PHHM exploits the other capabilities of PHHCD for calibration and operation.
    [000122] Four embodiments of the present invention will be described below by way of example, only with reference to the attached drawings, in which: Figure 1 shows a generic filtered and amplified signal acquired by an electrical sensor; Figure 2 schematically shows the variation in oxygenated blood signal (top line), deoxygenated blood signal (middle line) and ambient light signal (bottom line) acquired from a PPG sensor; Figure 3 shows a typical signal waveform of a heart lub-dub beat acquired by an acoustic sensor; Figure 4 shows the envelope derived from the acoustic signal of Figure 3; Figure 5 is a schematic illustration of a first embodiment of the present invention; Figure 6 is a schematic illustration of a second embodiment of the present invention; Figure 7 is a schematic illustration of a third embodiment of the present invention; Figure 8 is a schematic illustration of a fourth embodiment of the present invention; and Figures 9, 10 and 11 each show an arrangement for an optical sensor to be used in a PHHM of the present invention.
    [000123] It should be clearly understood that the following description of these three embodiments is provided purely by way of illustration, and that the scope of the invention is not limited to that description; rather, the scope of the invention is set out in the appended claims.
    [000124] Figure 5 shows the detail of a module, which is an embodiment of the invention, and the module installed in a cell phone. There is a flexible bellows (1) sealed at the end of the module housing (9). The bellows (1) is filled with an inert clear liquid. The bellows is transparent in the center, and around the transparent region is metallized to make electrical contact with a finger. Metallization can use micropyramids or other rough structures to improve electrical contact.
    [000125] One or more photoemitters (2) transmit light (shown by the dotted line) through the bellows (1). One or more photosensors (3) detect the light scattered back from a finger (15) pressed into the bellows (1).
    [000126] A pressure sensor (4) measures the pressure in the liquid. A temperature sensor (5) detects the temperature of any object in its field of view, which is above the module.
    [000127] The metallization, the photoemitter(s), the photosensor(s) and the temperature sensor are all connected to an electronic interfacial and control unit (6). A cable (7) from this unit connects to the cell phone processor using the I2C interface standard or another standard. A second cable (8) connects this unit to a pad (12) on the cell phone, used to make electrical contact with another finger.'
    [000128] The photoemitter(s), the photosensor(s), the temperature sensor and the electronic unit(s) can be separate silicon integrated circuits, or some or all of them can be combined in a single integrated circuit.
    [000129] The module is located in the top part of the cell phone casing (12), above the screen (11). A pad (14), for connection to a finger of the other hand, is located at the bottom of the cell phone casing. The user presses their finger (15) on the bellows (1) to take a measurement. The temperature sensor is behind a window (16).
    [000130] Figure 6 shows the detail of a second module, which is another embodiment of the invention, and the module installed in a cell phone. There is an inextensible strip (21) attached to the module body (29). The surface of the strap is metallized to make electrical contact with a user's finger.
    [000131] One or more photoemitters (22) transmit light (shown by the dotted line) along the strip. One or more photosensors (23) detect the light scattered back from the finger.
    [000132] There is a groove (24) in the body, below the point where one end of the strap is fastened. The bundle formed by this groove deforms when force is applied to the strip, and the deformation is measured by a strain gauge (25). A proximity sensor (31) measures the distance from the strip to the module body. A temperature sensor (26) detects the temperature of any object in its field of view, which is above the module.
    [000133] The metallization, the photoemitter(s), the photosensor(s), the strain gauge, the proximity sensor and the temperature sensor are all connected to an electronic interfacial and control unit (30). A cable (27) from this unit connects to the cell phone processor using the I2C interface standard or another standard. A second cable (28) connects this unit to a pad (34) on the cell phone, used to make electrical contact with a finger on the user's other hand.
    [000134] The photoemitter(s), the photosensor(s), the proximity sensor, the strain gauge, the temperature sensor and the electronic unit may be separate silicon integrated circuits, or some or all of them may be combined into a single integrated circuit .
    [000135] The module is located at the top of the cell phone casing (32), above the screen (33). The pad (34) for connection to a finger of the other hand is located at the bottom of the cell phone casing. The user presses their finger (35) on the strip to take a measurement. The temperature sensor is behind a window (36).
    [000136] Figure 7 shows the detail of a third module, which is another embodiment of the invention, and the installation in the cell phone. There is an extendable strap (41) which is fixed at one end of the module body (49), and at the other end it passes through a roller (45) to a spring (44). Inside the spring (not shown) is a sensor to measure its length. The strip surface is metallized to make electrical contact with a finger.
    [000137] One or more photoemitters (42) transmit light (shown by the dotted line) along the strip. One or more photosensors (43) detect light scattered back from the finger.
    [000138] A proximity sensor (51) measures the distance from the strip to the module body. A temperature sensor (46) detects the temperature of any object in its field of view, which is above the module.
    [000139] The metallization, the photoemitter(s), the photosensor(s), the spring length sensor, the proximity sensor and the temperature sensor are all connected to an electronic interfacial and control unit (50). A cable (27) from this unit connects to the cell phone processor using the I2C interface standard or another standard. A second cable (48) connects this unit to a pad (54) on the cell phone, used to make electrical contact with a finger on the user's other hand.
    [000140] The photoemitter(s), the photosensor(s), the proximity sensor, the spring length sensor, the temperature sensor and the electronics unit may be separate silicon integrated circuits, or some or all of them may be combined in a single integrated circuit.
    [000141] The module is located on the top of the cell phone casing (52) above the screen (33). The pad (54) for connection to a finger of the other hand is located at the bottom of the cell phone casing. The user presses their finger (55) on the strip to take a measurement. The temperature sensor is behind a window (56).
    [000142] Figure 8 shows the detail of a fourth module, which is another embodiment of the invention, and the installation in the cell phone. There is a plate (61) in which a button (62) is inserted so that the top part of the button (62) is flush with the plate. The button (62) is supported by a force sensor (63). One or more photoemitters (64) transmit light (shown by the dotted line) through the top portion of the button (62). One or more photosensors (65) detect light scattered back from a finger pressed to the button (62). The top part of the button (62) is metallized (not shown).
    [000143] The metallization, the photoemitter(s), the photosensor(s) and the force sensor are all connected to an electronic interfacial and control unit (66). A cable (67) from this unit connects to the cell phone processor using the I2C interface standard or another standard. A second cable (68) connects this unit to a pad (73) on the cell phone, used to make electrical contact with a finger on the user's other hand.
    [000144] For calibration, the PHHCD can be oriented by the user to be pointing up or down, and the orientation can be detected by using existing sensors on the PHHCD. The variation in signal from the force sensor, under the weight of the knob in these two orientations, can be used to calibrate the force sensor.
    [000145] A temperature sensor (69) can either be contained within the knob (62) or located separately and connected to the knob (62). The module is located at the bottom of the cell phone casing (71) below the screen (72). The pad (73), for connection to a finger of the other hand, is located on the top part of the cell phone casing.
    [000146] Figures 9, 10 and 11 show three arrangements of optical sensors, which will be used in the PHHM of the present invention to measure the concentration of an analyte in the blood. It can be built into a PHHCD, or it can be connected to a PHHCD, or it can be built as a dedicated device with its own user interfaces, power supply, and other electronic and mechanical components. The means of photoplethysmography or the mechanism for modulating the intensity of the light beam is not shown. The three illustrations show optical and other distinct components; alternatively, the sensor can be implemented as one or more integrated optical devices, in which several optical components are formed into a single block of transparent plastic.
    [000147] In Figure 9, the light source (81) transmits a light beam, which passes through a filter (82) to select the spectral range of light to be used. The spectral range is selected to allow inexpensive components and materials to be used, while maximizing sensitivity and discrimination against the analyte. The beam is collimated by a lens (83) to shine through a bodily part such as a finger (84). A beam splitter (85) splits the beam between a reference cell (86) and the sample cell (87). Photosensors (88) measure the intensity of the beam after it has passed through each cell. A differential amplifier can be used to amplify the difference in signal between the two photosensors.
    [000148] Figure 10 shows another implementation in which a sample cell (96), containing gaseous analyte, has one or more walls forming a diaphragm (109), moved by an actuator (99).
    [000149] Figure 11 shows another implementation in which the light source and detectors are on the same side of a body part, the detectors being sensitive to light scattered back from the body part. A movable mirror (101) reflects light sequentially to each of the two fixed mirrors (102), and therefore to the reference cell or sample cell. One or more photosensors (108) measure the intensity of the beam that has passed through the cells.
    [000150] All illustrated embodiments of PHHM include one or more electronic components (not shown), which may include: one or more pressure sensors, one or more analog-to-digital converters, one or more temperature sensors, a unique identifier and an interface to the cell phone's electronic circuits.
    权利要求:
    Claims (3)
    [0001]
    1. Personal portable monitor (PHHM) comprising a signal acquisition device for signal acquisition that can be used by a PHHM processor to derive a measure of a parameter related to the user's health, the signal acquisition device being integrated with a portable personal computing device (PHHCD), wherein the parameter is blood pressure and the signal acquisition device comprises a blood flow occlusion means (1, 21, 41, 62), adapted to be pressed against one side only. of a bodily part, or having only one side of a bodily part pressed against it, a means for measuring the pressure (4, 63) applied by or on the bodily part, and characterized in that it further comprises: a means for detecting the blood flow (3, 23, 43, 65) through the body part in contact with the blood flow occlusion means (1, 21, 41, 62), where: the means to detect blood flow (3, 23, 43 , 65) is an optical sensor (88, 108), and the process The PHHM sensor (6, 30, 50, 66) is adapted to detect flow over a range of pressures applied by or to the body in any order and to estimate systolic and diastolic pressures using an oscillometric method by adjusting the measured pressure and the flow data into a theoretical curve relating blood flow range to external applied pressure.
    [0002]
    2. Personal portable monitor according to claim 1, characterized in that the PHHM is adapted to provide audible or visual instructions to the user to adjust the force with which the blood flow occlusion means (1, 21, 41, 62) is compressed in the body part, or whereby the body part is compressed in the blood flow occlusion means (1, 21, 41, 62), in response to the PHHM signals, in order to ensure that measurements are at a sufficient range of applied forces to allow estimation of systolic and diastolic blood pressures.
    [0003]
    3. Personal portable monitor according to claim 1 or 2, characterized in that the blood occlusion means (1) comprises a pad (1) filled with a fluid and the means for measuring pressure (4) includes a sensor (4) to determine the pressure in the fluid.
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    法律状态:
    2018-12-11| B06F| Objections, documents and/or translations needed after an examination request according [chapter 6.6 patent gazette]|
    2019-12-10| B06U| Preliminary requirement: requests with searches performed by other patent offices: procedure suspended [chapter 6.21 patent gazette]|
    2021-06-15| B09A| Decision: intention to grant [chapter 9.1 patent gazette]|
    2021-07-27| B16A| Patent or certificate of addition of invention granted [chapter 16.1 patent gazette]|Free format text: PRAZO DE VALIDADE: 20 (VINTE) ANOS CONTADOS A PARTIR DE 26/06/2012, OBSERVADAS AS CONDICOES LEGAIS. |
    优先权:
    申请号 | 申请日 | 专利标题
    GB1111138.2|2011-06-30|
    GBGB1111138.2A|GB201111138D0|2011-06-30|2011-06-30|Personal health data collection|
    GB1200794.4|2012-01-18|
    GBGB1200794.4A|GB201200794D0|2011-06-30|2012-01-18|Personal health data collection|
    PCT/GB2012/000549|WO2013001265A2|2011-06-30|2012-06-26|Personal health data collection|
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