Classifications

• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
  • A61B5/021—Measuring pressure in heart or blood vessels
  • A61B5/022—Measuring pressure in heart or blood vessels by applying pressure to close blood vessels, e.g. against the skin; Ophthalmodynamometers
  • A61B5/02233—Occluders specially adapted therefor
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
  • A61B5/021—Measuring pressure in heart or blood vessels
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
  • A61B5/02007—Evaluating blood vessel condition, e.g. elasticity, compliance
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
  • A61B5/021—Measuring pressure in heart or blood vessels
  • A61B5/02108—Measuring pressure in heart or blood vessels from analysis of pulse wave characteristics
  • A61B5/02125—Measuring pressure in heart or blood vessels from analysis of pulse wave characteristics of pulse wave propagation time
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
  • A61B5/021—Measuring pressure in heart or blood vessels
  • A61B5/02133—Measuring pressure in heart or blood vessels by using induced vibration of the blood vessel
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
  • A61B5/026—Measuring blood flow
  • A61B5/0285—Measuring or recording phase velocity of blood waves
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
  • A61B5/026—Measuring blood flow
  • A61B5/029—Measuring or recording blood output from the heart, e.g. minute volume
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
  • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
  • A61B5/6802—Sensor mounted on worn items
  • A61B5/681—Wristwatch-type devices
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B2560/00—Constructional details of operational features of apparatus; Accessories for medical measuring apparatus
  • A61B2560/02—Operational features
  • A61B2560/0223—Operational features of calibration, e.g. protocols for calibrating sensors
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
  • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
  • A61B2562/0219—Inertial sensors, e.g. accelerometers, gyroscopes, tilt switches
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
  • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
  • A61B2562/0247—Pressure sensors
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
  • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
  • A61B2562/0261—Strain gauges
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
  • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
  • A61B2562/028—Microscale sensors, e.g. electromechanical sensors [MEMS]
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
  • A61B5/024—Detecting, measuring or recording pulse rate or heart rate
  • A61B5/02416—Detecting, measuring or recording pulse rate or heart rate using photoplethysmograph signals, e.g. generated by infrared radiation
  • A61B5/02422—Detecting, measuring or recording pulse rate or heart rate using photoplethysmograph signals, e.g. generated by infrared radiation within occluders

Definitions

• the invention relates to the time-resolved measurement of blood pressure, arterial elasticity, pulse wave, pulse wave transit time and pulse wave velocity, and / or
• the measurement of time-resolved changes in cardiac output requires the measurement of many other characteristics of the cardiovascular system. These include the time change of blood pressure, the pulse wave transit time, respiratory rate and heart rate.
• the invention enables a temporal resolution in the millisecond range.
• the blood pressure is not only measurable in the form of systolic and diastolic blood pressure, but also as a continuous wave, which indicates at any time, even within a single heart pulse, the current pressure on the arteries.
• the invention also relates to a pressure sensor unit for time-resolved pressure measurement and a method and a use for pressure measurement in general.
• the system according to the invention for, in particular time-resolved, measurement of blood pressure, arterial elasticity, pulse wave transit time, pulse wave velocity, pulse wave and / or changes in cardiac output and / or cardiac output
• the pressure sensor unit for time-resolved pressure measurement of the pressure exerted on the skin by a pulse pressure
• the pressure sensor unit is an air and / or gas pressure sensor and / or is set to at least one electrical conductance and / or resistance upon application of pressure to change.
• the pressure sensor unit has at least two conductor track arrangements, in particular printed conductor networks, and a functional polymer which is adapted to be compressed by the application of pressure and to establish and / or change the contact between the conductor track arrangements.
• the pressure sensor unit may have at least two conductive layers with a space disposed therebetween, and the
• Pressure sensor unit be set up so that by applying pressure to the
• Interspace is compressed and / or thereby changes in particular the capacity of the arrangement consisting of the two conductive layers.
• the intermediate space is formed in particular by at least one dielectric.
• Pressure sensor unit and / or an air and / or gas pressure sensor used as a pressure sensor unit advantageously capacitances are detected and / or measured instead of conductance and / or resistances and in particular for pressure determination
• an electrical Property detected and / or measured and used in particular for pressure determination instead of conductivities and / or resistances, an electrical Property detected and / or measured and used in particular for pressure determination.
• the dielectric may be formed by a functional polymer.
• the functional polymer may be or include a dielectric.
• the pressure sensor unit can have at least two conductive layers and / or conductor arrangements with a volume and / or material arranged therebetween and / or the material and the pressure sensor unit can be set up in such a way that the volume and / or material is compressed by applying pressure and / or characterized in particular changes an electrical property of the arrangement consisting of the two conductive layers and / or conductor track arrangements.
• the volume and / or material is formed and / or has in particular by at least one dielectric and / or functional polymer.
• the volume and / or material, the dielectric and / or the functional polymer are in particular designed so that they exert a restoring force against compression.
• the system has an actuator which is set up to press the sensor unit against the skin.
• the system has in particular a device for measuring the conductance of the at least one pressure sensor unit.
• the system is set up to measure the conductance and / or pressure with at least a temporal resolution of 5 ms, in particular 2 ms, in particular 1 ms.
• the system is set up to determine pressure values from the guide values, in particular by means of a conversion and / or assignment which has been obtained, in particular, by a calibration.
• the pressure sensor unit has at least one arrangement of, in particular exposed, printed conductors and / or conductor networks and a resistance-conductive and / or conductive polymer, which may be part of the functional polymer, which is pressed onto the at least one arrangement of printed conductors by applying pressure.
• the pressure sensor unit has at least one non-conductive polymer, which is arranged between two arrangements of at least one conductor track and has holes. The conductor tracks are formed in particular freely in the holes.
• the object is also achieved by using the change of a capacitance, a conductance and / or the change of a resistance and / or a conductance and / or a resistance between at least two conductive layers and / or between at least two conductor track arrangements, in particular printed conductor networks, by compression of a functional polymer and / or dielectric by pressure applied to the skin over an artery by a pulse wave for time resolved measurement of blood pressure, arterial elasticity, pulse wave transit time, pulse wave velocity, pulse wave, and / or changes in cardiac output and / or of cardiac output.
• a pressure sensor unit according to the invention for example on a gripping system, in particular a robot hand, and the Use of a pressure sensor unit according to the invention on a gripping system, in particular a robot hand, for measuring the pressure force of the gripping system and a method for gripping an object with a gripping system
• At least one pressure sensor unit so that the pressure force of the gripping system acts on the object on the pressure sensor unit and measuring at least one electrical property, in particular conductance, resistance and / or capacitance, or their change to the time-resolved determination of the pressure force and by a method for producing a pressure sensor unit.
• the object is also achieved by one or a plurality of pressure sensor unit (s) according to the invention, for example as a sensitive shell and / or sensitive surface or artificial skin or in such a, in particular a robot, and the
• one or a plurality of pressure sensor unit (s) as sensitive shell and / or sensitive surface or artificial skin or in such, in particular a robotic skin, for measuring the forces on the sensitive shell and / or sensitive surface or artificial skin and a by methods for measuring the forces on a sensitive sheath and / or a sensitive surface or artificial skin comprising at least one or a plurality of inventive (r)
• Pressure sensor unit (s) so acting on the sensitive shell and / or sensitive surface or artificial skin forces acting on the pressure sensor unit (s) and measuring at least one electrical property, in particular conductivity, resistance and / or capacity, or their change to the time-resolved determination of Forces on the skin.
• the object is also achieved by a sensitive shell and / or sensitive surface or artificial skin or in such, in particular a robot, comprising a plurality of inventive pressure sensor units.
• the pressure sensor unit according to the invention is suitable for such applications, especially due to the possibility to detect forces in different measuring ranges with different accuracies with a single pressure sensor unit, then with such a sensitive shell and / or sensitive surface or artificial skin, in particular using the same or structurally identical Pressure sensor units are measured both the blood pressure of a living being, as well as significantly higher forces or pressures, such as when grasping heavy objects or of 1 000kPascal or
• the at least one pressure sensor unit is designed to measure pressures between 6kPascals and 1000kPascals.
• the sensitive shell and / or sensitive surface or artificial skin may
• the artificial skin comprises a sensor array of a plurality of pressure sensor units.
• the object is also achieved by a method for, in particular time-resolved, pressure measurement, in particular the blood pressure, the
• Circuit arrangements in particular printed conductor networks, and / or conductive layers by compressing a functional polymer, interspace, dielectric, volume and / or material, in particular by the pressure exerted on the skin over an artery by a pulse wave pressure.
• the functional polymer, the intermediate space, the dielectric, the volume and / or the material is in particular between and / or on the at least two conductor track arrangements, in particular
• Conductor networks and / or conductive layers arranged.
• the conductor track arrangements and / or conductive layers and the functional polymer, the gap, the dielectric, the volume and / or the material are in particular part of a pressure sensor unit described in this document.
• the pressing is carried out in particular with a pressure in the range of 50 and 300 mmHg and / or between 6kPascal and 40kPascal.
• the pressure can be transmitted by pressing a pressure sensor unit, in particular designed as described in this document, and / or
• the pressurization can be used in particular for pressing.
• the pressurized gas has a pressure between 50 and 300 mmHg and / or between 6kPascal and 40kPascal.
• the conductor track arrangements and the functional polymer are pressed against the skin with different pressure and the conductivity is measured and / or the change in the conductance is determined, in particular at least with a temporal resolution of 5 ms, in particular 2 ms, in particular 1 ms different pressure monotonically and / or continuously increased, in particular until a further increase in the backpressure and / or contact pressure, the pulse wave can produce no increase in the measured pressure beyond the maximum measured pressure addition, wherein the pressing is carried out in particular by inflating an airbag or by another actor.
• An airbag is in particular a device with enclosed volume, in particular with a flexible envelope, for example, a pressure pad understood.
• An airbag is in particular designed to be pressurized by the supply of gas, in particular by expansion of its volume. It is in particular formed by pressurizing the airbag, onto an object circumscribed by the airbag, for example an arm, or a circularly circumscribed object, for example an arm which is surrounded by a surrounding device and in particular the airbag in a circular manner, the airbag in particular is arranged between circularly surrounded object and enclosing device, but itself does not surround the enclosed volume, in particular, to exert pressure.
• a blood pressure measurement using other means for example a previously known blood pressure measurement and / or with previously known blood pressure measuring means and / or procedures, is performed and / or other means for blood pressure measurement, such as a microphone and / or stethoscope for classical blood pressure measurement in the system includes or is used.
• another pressure sensor which may be included in the system, can be used to make a blood pressure measurement. Parallel and / or in close temporal relation of max. 10
• Seconds distance to this blood pressure measurement in particular at least air or gas pressure, capacitance, conductance and / or resistance, in particular with at least a temporal resolution of 2ms, in particular 1 ms, measured, in particular, at least one pressure sensor unit and is based on the measurements of Blood pressure using the other means and / or prior art blood pressure measuring means and / or - methods and a calibration of the air or gas pressure, capacitance, conductance and / or resistance measurement to subsequently allow blood pressure measurements by means of at least one pressure sensor unit and / or perform.
• Blood pressure measuring means and / or methods work in particular by increasing the pressure in the air pressure cuff and measuring the pressure in the air pressure cuff or a fluidically connected volume.
• the pulse wave causes a fluctuation in the measured pressure, which drops as the pressure in the air pressure cuff increases further.
• the course of these fluctuations shows a time course. From this time course and / or the envelope of the fluctuations, the diastolic and / or systolic blood pressure is derived in the prior art.
• such a system can also be used according to the invention for measuring the pulse wave or for determining the blood pressure at a pulse wave.
• at least one measurement is carried out according to the previously known method and used to calibrate the measured values of the air or gas pressure, capacitance, conductance and / or resistance measurement in order to derive the pressure of the pulse wave directly from these measured values.
• Systems, methods and / or uses according to the invention are thus especially arranged and / or designed such that values of systolic and / or diastolic blood pressure, arterial elasticity, pulse wave pressure, pulse wave transit time and pulse wave velocity and / or cardiac output changes and / or the cardiac output in each case based on a pulse wave and not based on a plurality of pulse waves, as given for example in the described prior art derivative of the envelope.
• the at least one pressure sensor unit can be pressed, for example, through the airbag onto the skin via an artery.
• the effect of the pulse wave on the gas contained in the air bag under pressure can be transmitted through the air bag.
• the pressure of the gas in the airbag is in particular between 50 and 300 mmHg and / or between 6kPascal and 40kPascal and / or is in particular constructed by the actuator.
• the pressure sensor unit can thus also be arranged so that it can detect the pressure fluctuation in the gas of the airbag.
• the systolic blood pressure is presumed to be the pressure at or from which, with further increase in backpressure and / or contact pressure, the pulse wave can not produce an increase in measured pressure beyond the maximum measured pressure and / or the diastolic blood pressure is assumed to be the pressure which corresponds to the minimum of the measured values of a pulse wave, if the backpressure and / or contact pressure is selected as the pressure or higher, at which the maximum measured pressure does not increase further as the backpressure and / or contact pressure increases.
• a particular advantage of the invention is that the values, such as systolic blood pressure and diastolic blood pressure, can be determined non-invasively from a single pulse wave, which is preferred, and is also directly related physically and physiologically.
• the pressure of the pressing is subsequently reduced and / or after determination of a systolic blood pressure, in particular to a value within a range from the determined diastolic to the ascertained systolic blood pressure and / or up to 1.5 times, in particular 1.3. times, systolic pressure pressure of
• the pressure of the pressing is subsequently and / or after ascertaining a systolic blood pressure and / or under knowledge of a first systolic blood pressure and / or a first conductance of the at least one pressure sensor unit
• Pulse wave transit time to determine the current pulse wave velocity, the current pulse wave and / or the current change in the cardiac output and / or the current cardiac output.
• the method is carried out by means of a system according to the invention.
• the object is also achieved by using the change of an electrical property, in particular a capacitance, a conductance and / or an electrical property, in particular a capacitance, a resistance and / or a conductance between at least two conductive layers and / or between at least two conductor track arrangements , in particular printed circuit networks, by compressing a functional polymer, a gap, dielectric, volume and / or material by the pressure exerted on the skin over an artery by a pulse pressure for the time-resolved measurement of the blood pressure, the arterial elasticity, the Pulse wave transit time, the pulse wave velocity, the pulse wave and / or changes in the cardiac output and / or and or cardiac output.
• an electrical property in particular a capacitance, a conductance and / or an electrical property, in particular a capacitance, a resistance and / or a conductance between at least two conductive layers and / or between at least two conductor track arrangements , in particular printed circuit networks
• the object is also achieved by a method for retrofitting previously known air pressure measuring systems having an air pressure cuff, a device for pressurizing the air pressure cuff and an air and / or gas pressure sensor, wherein the air pressure measuring system is provided with an evaluation device, which is for carrying out a method according to the invention, in particular in a is designed as advantageously described, and / or already included
• Evaluation device is changed so that they carry out a
• inventive method in particular in an embodiment described as advantageous, is set up.
• the advantageous embodiments relating to the method, the pressure sensor unit, the system and / or the use can be transferred to the method, the pressure sensor unit, the system and / or the use.
• a polymer which conducts resistance and / or conducts can be produced in two ways.
• the polymer can be chemically constructed in such a way that an intrinsic conductivity is present, for example by conjugated double bonds of the carbon atoms in the polymer chains. This type of polymer is a younger and rarely used one
• conductive materials may also be incorporated into a conventional polymer. This can e.g. Carbon black, graphite or metal particles, in particular of the order of a few nanometers.
• an ink may e.g. from the company Loctite. Typically, such an ink consists of a solubilized thermoplastic which is coated with electrically conductive particles, e.g. Graphite, is offset. These inks have optimum electrical properties, but their abrasion is poorly degraded, which makes them very resistant to abrasion
• thermoplastic is a polymer in which the individual polymer strands are loose, comparable to spaghetti. An improvement in the abrasion behavior can be achieved by the individual polymer strands are linked together, the material is rather rubbery or turns into an elastomer.
• Crosslinking can occur during production by introducing various catalysts, for example vulcanisers such as sulfur, into the ink and / or the resistance-conductive and / or conductive polymer. Subsequent networking is complicated and usually costly. Thus, free radicals can be generated in the resistance-conductive and / or conductive polymer. These attack the polymer chains and create reactive sites that react with other chains to create a network. These radicals can be generated either by radiation or by chemical substances. In the radiation usually electron beams is used. In chemical treatment, peroxides are introduced into the polymer, which gradually disintegrate and release free radicals.
• catalysts for example vulcanisers such as sulfur
• the conductive polymer is usually a thin layer, chemical crosslinking is possible. Liquid peroxides can diffuse into the material and also in the material (but close to the surface) cause chemical reactions. For a given exposure time, a higher crosslinking and thus a higher stability in the surface material can be produced.
• the temperature can be increased.
• the polymer can swell by a solvent, whereby an increased diffusion into the material is possible.
• the first method uses temperatures of 120-160 ° C. In this temperature range, however, are also the melting temperature of many thermoplastics accurate temperature control is necessary.
• the second method is also problematic since mixtures of peroxides and
• Solvents is the basis of many explosives.
• Time-resolved and / or time-resolved means, in particular, that the measurement takes place with a temporal resolution or the system is set up for a measurement with a temporal resolution, which allows the pressure maxima and pressure minima of a
• the measurement and / or the system is set up for a measurement, in particular of at least one electrical conductivity, resistance and / or at least one capacitance, with a repetition rate of at least 100 Hz, in particular at least 500 Hz, in particular at least 800 Hz, in particular at least 1 kHz ,
• the determination of the parameters of the cardiovascular system is based on the analysis of the measurements of the pulsating pressure wave from the heart in the arteries.
• the measured values also referred to as measured value wave in their time sequence, can be examined for minima and maxima of the pulsating pressure wave. The values of these minima and maxima are correct
• the current heart pulse can be determined and that from pulse to pulse, which allows the calculation of the pulse wave variability.
• the simultaneous determination of cardiac pulse and blood pressure allows the calculation of cardiac output.
• An arrangement or system according to the invention can also have several
• Pressure sensor units feature.
• the pulse wave transit time can be determined by multiplying, at least two,
• Pressure sensor units and / or at least one pressure sensor unit and a device for measuring the pressure wave and / or the pulse at at least two measuring points on the body record the pulsating pressure wave and / or the pulse.
• the time interval between two maximas and / or correlating events which are due to the same heart pulse are used to determine the pulse wave transit time between the measuring points and in particular the distance of the measuring points and / or the distance of the measuring point to the heart, the pulse wave velocity.
• the pulse wave transit time can also be determined by analyzing the measured values of the pulsating pressure wave by determining the reflection wave and determining the time interval of the reflection wave and the initial wave as the pulse wave transit time.
• the pulse wave When the heart pushes out the blood, the pulse wave first enters the aortic arch, then this artery branches into smaller arteries. Because of the differences in
• Diameter before and after a branching it comes to reflection with each branching.
• the largest reflection of the amplitude arises in the smallest arteries and this can be detected in the pressure wave.
• the pulse wave velocity can be determined from the pulse transit time with knowledge of the distance of the measurement sites from each other and / or the distance of the measurement site from the heart.
• the elasticity of the arteries can be calculated from the pulse wave velocity e.g. be determined with the Moens-Korteweg formula.
• the temporal resolution of data acquisition also allows the distance of the sensors from each other need not be particularly large, and thus a system with multiple pressure sensor units can be used, which is perceived by the user as a single unit , This allows a very simple and rapid measurement of these parameters, which require lengthy preparation times and a large number of different sensors with measuring devices used today.
• the system or pressure sensor unit is applied at a suitable location, particularly at a location over an artery, e.g. be a spot on the wrist, and then slowly pressed. Pressing with a suitable location
• Contact pressure or the setting of the back pressure can be done either by human action or by an autonomous actuator. At the same time, measured values of the
• Pressure sensor unit in particular conductances, from which a pressure can be derived, which are influenced by the pulsating pressure wave of the artery detected.
• Counterpressure or contact pressure in particular from a value of 60mmHg or less, increases, the maximums of the detected pressure and / or the measured value wave and / or the measured values also increase. From a certain contact pressure or back pressure is no further
• the pressure value of a maximum of the pressure and / or the pressure associated with a maximum of the guide values is the value of the systolic blood pressure. At the smallest contact pressure and / or counterpressure, in which no further increase of the maxima of the measured value wave and / or the measured values can be recognized, corresponds to
• a maximum corresponds to a systolic blood pressure of a pulse wave and a minimum to a diastolic blood pressure of a pulse wave.
• associated pressure represents the value of the systolic blood pressure of the respective pulse wave and / or any pressure value of a minimum of the measured value wave and / or any pressure associated with a minimum represents the diastolic blood pressure of a pulse wave.
• the method is carried out and / or the system is designed so that at least one pressure value, in particular at least two pressure values, at least every twentieth, in particular at least every tenth, in particular every second or each pulse wave, in particular of at least 50, in particular of at least 500, consecutive pulse waves, determined and / or displayed.
• at least one pressure value in particular at least two pressure values, at least every twentieth, in particular at least every tenth, in particular every second or each pulse wave, in particular of at least 50, in particular of at least 500, consecutive pulse waves, determined and / or displayed.
• at least one pressure value in particular at least two pressure values, at least every twentieth, in particular at least every tenth, in particular every second or each pulse wave, in particular of at least 50, in particular of at least 500, consecutive pulse waves, determined and / or displayed.
• 5 to 20 pressure values and / or pressure values for 5 to 20 pulse waves are displayed.
• the method is carried out and / or the system is designed so that continuously, so in particular at least every twentieth, especially measured at least every tenth, in particular every second or each pulse wave of at least 500 consecutive pulse waves and / or at least every twentieth , at least every tenth, in particular every second or every pulse wave of at least 500 consecutive pulse waves at least one blood pressure value, an arterial elasticity value, a pulse wave transit time value, a pulse wave velocity value and / or a cardiac output change value and / or a value of
• Cardiac output and / or is displayed In particular, 5 to 20 values and / or values of 5 to 20 pulse waves are displayed at the same time.
• the method is particularly advantageously carried out such that the blood pressure, the arterial elasticity, the pulse wave transit time, the pulse wave velocity, the pulse wave and / or changes of the cardiac output and / or the cardiac output
• Cardiac output in particular the pressure curve of the pulse wave, is measured on at least two, in particular four, extremities and the measured values of the measurements on the extremities are compared, in particular those which are attributable to the same heartbeat.
• the system is arranged to measure blood pressure, arterial elasticity, pulse wave transit time, pulse wave velocity, pulse wave, and / or changes in cardiac output and / or heart rate
• Cardiac output in particular the pressure curve of the pulse wave, at least two, in particular four, extremities, wherein it has at least one pressure sensor unit per extremity and to compare the measured values of the measurements on the extremities, in particular those measured values that are due to the same heartbeat.
• the maxima and / or minima are in particular local maxima and minima.
• Calibrations presented here are not to be performed by the user, but can be automated or made during production.
• an acceleration sensor in this patent is based on the fact that the value of the blood pressure at different points in the body and also at different heights to the hydrostatic indifferent point (HIP) (changes in the height of a measuring point to the HIP is triggered, for example, on the arm by an arm movement).
• HIP hydrostatic indifferent point
• a value for the blood pressure at the HIP can also be determined in the movement, even though the measuring point is located, for example, on the arm.
• a sensor array can be used to determine the pulse transit time at the measuring point by evaluating the measured values of the pulsating pressure wave from at least two pressure sensor units of the sensor array. In particular, at least two maxima of the measured values of the pulse wave are used, which are attributable in particular to the same heartbeat. In particular, with a known distance between the at least two pressure sensor units can then be,
• a plurality of sensors may be organized separately from each other so that one sensor may be mounted near the heart, for example, and another may be attached to the wrist at a suitable location, for example.
• the evaluation of the measured value wave of the pulsating pressure wave enables the calculation of the pulse wave transit time from the heart to the wrist.
• the invention does with a minimum sensor size and requires no invasive intervention in the body.
• the sensor can be placed directly on the skin, see Fig. 1 letter O.
• the size of the pressure sensor unit in particular your pressure-sensitive surface and / or
• Support surface on the skin not larger than a cherry stone and or smaller than 15 mm, in particular less than 10 mm, in particular less than or equal to 5 mm in diameter, in particular in order to carry out a blood pressure measurement on the skin.
• the operation of the invention is based on the operation of the classical method for blood pressure measurement, the Riva Rocci method. However, this extends the temporal resolution of blood pressure value determination and can therefore also be used for continuous long-term measurement. In addition, the measurement is due to the small
• the pressure sensor units and an evaluation unit can be used alone.
• the pressure sensor unit is integrated with an evaluation unit and / or energy unit and / or radio unit in a system and / or a device and / or in a garment and / or designed as an essay.
• Possible garments are bracelets, footbands, shoes, rings or ear clips. Furthermore, the inventive arrangement can also be attached to the body with the help of specially made straps.
• inventive arrangement and / or the system designed as essay this (s) by attaching to a conventional bracelet or, for example, by attaching or inserting the shoe / tongue (back of the foot) are attached to the body.
• inventive arrangement and / or the system can also be extended by an actuator which a base pressure or contact pressure on the
• the inventive arrangement can be mounted on the body so that pressure can be applied to the body by the pressure sensor unit.
• places on the body are advantageous in which the pulse of the arterial system is noticeable. These are, for example, under other positions on the wrists or positions on the backs of the feet.
• FSR sensor Force Sensing
• Resistor for the measurement of blood pressure as a pressure sensor unit application.
• This technology is described in a patent by Interlink and in a variety of publications by the company Interlink accessible to the skilled person on the Internet.
• This described pressure sensor is also produced by the company Interlink and has been commercially available for many years.
• the pressure sensor is available in different sizes.
• the FSR sensors listed below function by applying an electrically conductive paste or substance to the carrier material, but above the electrical leads.
• a pressure-sensitive and resistance-conductive film is used, which is applied with a carrier layer to the electrical conductor tracks and connected to each other by means of double-sided adhesive layer.
• the person skilled in the necessary information is available.
• the offerings of the company "Interlink" to FSR sensors are limited to a pressure-sensitive film that changes their resistance conductivity when exposed to pressures or weights.
• the FSR sensors technology was not for accurate and continuous
• a calibration of the conventional sensors can be done by loading the sensor with a known pressure.
• This may, for example, be a motorized bracelet which sets a known pressure by defined contraction.
• This pressure of the bracelet may e.g. by strain gauges (these are not usable for the actual measurement because the temporal resolution is too low) can be determined.
• vibration motor and / or by varying the contact pressure by the
• Vibration motor performed. This can be done by suitable electrical circuit, the
• a pressure sensor unit may be attached to the inside of a belt. Between sensor and belt, the vibration motor can be arranged.
• Enclosing device and pressure sensor unit arranged.
• the invention prefers small and in their application for blood pressure measurement specific designs, in particular in the form of an elastic molding, as a solution.
• a small sensor size advantageously with a diameter of 5mm or smaller.
• larger and smaller sizes are possible and / or
• a measuring range covering the expected blood pressure range should be at least 40mmHg or 5kPascal and / or up to 300mmHg or 40kPascal and / or
• the sensor should attenuate the signal as little as possible and / or
• the invention particularly uses new types of sensors as
• Pressure sensor unit which will be presented below, but also the use of an FSR sensor or piezo sensor as a pressure sensor unit is possible.
• an SRS sensor switchable resistive sensor
• This sensor type has several measuring ranges (at least two different measuring ranges). This makes it possible, for example, to jointly cover a large measuring range, which is given by the sum of the measuring ranges and / or to cover one or more measuring ranges with different accuracies.
• the measuring areas overlap at least partially and / or they have different sizes and / or spans.
• different resolutions of the measurement, in particular of the pressure result from different ranges for the same absolute changes in conductance over the respective measuring ranges and the same measuring accuracy.
• the individual measuring ranges are independent of each other, i. the measurement of blood pressure is simultaneous in the different
• the admission areas overlap.
• FSR sensors Force Sensing Resistor
• a large total measuring range can be recorded. This is particularly advantageous since during the movement of the body, the time-varying blood pressure signal due to the height of the sensor, measuring point, for example. At the extremities, varies to the HIP.
• the variation of the blood pressure signal can have several causes.
• Drugs lead to a sudden change in the blood pressure signal.
• SRS sensors have at least three
• VSR sensors also have only two, in particular, for the reading of the conductance values and / or resistances
• Track network has at least one conductor section, in particular a plurality
• interconnect arrangements or interconnect networks are interlocked in particular and / or in particular have a parallel interconnect section.
• the conductor tracks, conductor track sections or conductive layers may, for example, be metallic and / or doped semiconductors and / or be formed by conductive polymer.
• Conductive layers are formed in particular flat without holes or recesses.
• a conductive polymer typically has a higher resistance than a metallic conductor, such as copper. Therefore, only that with conductive polymer should be printed or executed, which is absolutely necessary, otherwise either a higher energy requirement is expected or the signal quality may suffer. In the case of digital lines, the signal transmission may be affected by too long polymer conductors.
• Conductive polymers have in addition to the resistance in the conductor also an increased contact resistance. This means that in a simple pressing of a metallic conductor on a polymer conductor (for example by crimping) is usually not good contact to produce. However, a transition from polymer to metallic conductors is usually unavoidable.
• the end of the metallic conductor may be formed in the form of a net or one or more eyelets
• the SRS sensor transmits the signal of the pulsating pressure wave through the at least three interconnects or conductive layers having multiple sensing areas simultaneously can, without switching the readout electronics, the best measuring range can be used.
• VRS Very Resitive Sensor
• the conductor track arrangement can be selected to determine the conductance values and / or resistances as in the case of FSR sensors, but in addition the polymer is changed in its sensitivity by an electrical induction.
• Range selection is arbitrary by the degree of electrical induction.
• the conductor track arrangements, conductor track networks and / or at least one conductive layer are arranged in particular on an electrically insulating carrier layer.
• a fixed measuring range can be set, which is only changed if necessary, the signal of the pulsating pressure wave is measured directly.
• the pressure can also be measured indirectly by changing the electrical induction to range selection until a given signal results.
• the actual measured value here is the setting of the electrical induction.
• the direct measurement allows a faster generation of measured values, whereas the indirect measurement allows more accurate measurements.
• the basic structure of the tracks of a VRS sensor is in particular analogous to the structure of an SRS sensor with two measuring ranges, ie with three interconnect networks.
• a third interconnect network an electrode and / or third conductive layer is used together with another (fourth) conductive layer on the opposite side (as viewed from the interconnect networks) of the functional polymer.
• a voltage is applied, in particular to Induce a voltage and / or the
• the functional polymer has the property of reacting to this applied voltage.
• the reaction consists in a change of the measuring range. There are two mechanisms of action that can be exploited individually or together. On the one hand, the electrical conductivity of the polymer can be changed. On the other hand, the mechanical properties can be changed.
• An example of a functional polymer that may alter its electrical properties is a non-conductive soft base material in which elongated electrically conductive particles are incorporated. In addition, the particles have an electric dipole moment.
• electroactive polymers that can change their mechanical properties by applying an electrical voltage are summarized under the collective term electroactive polymers.
• the polymer Nafion can be used. This deforms when a voltage of 1 to 5V is applied.
• electroactive polymer may be applied from both sides of an electrical surface and deformable contact. On one of these electrical contacts will
• a layer of electrically conductive polymer applied advantageously, a non-conductive layer is applied between the electrical contact and conductive polymer.
• the thickness of the electroactive polymer may be constructed concentrically decreasing outwards, whereby a hemispherical deformation is triggered.
• the polymer is restricted in its movement, whereby the thus deformed polymer is pressed onto the conductor tracks.
• the electroactive polymer presses against the tracks and less external stress is needed to obtain the same reading when there is no deformation of the polymer.
• the measuring range is shifted to smaller loads.
• the sensor types themselves represent an electrical resistance, which change their resistance value by force or pressurization.
• the SRS has different resistors for different measuring ranges, the VRS sensor in particular only via a resistor.
• VRS sensors and SRS sensors can be combined in a pressure sensor unit by changing the measuring range of an SRS sensor by inducing it into the functional polymer of the SRS sensor or the pressure sensor unit.
• the printed conductors and / or networks and / or sections are in particular insulated from one another.
• the sensors presented here are based on the fact that a polymer, including functional polymer, which is resistant to conductivity and / or conductive and / or a
• Resistive conductive and / or conductive surface is pressed on an array of, in particular exposed, printed conductors by the action of force.
• the printed conductors should not be completely exposed, but should be so exposed that the functional polymer can contact them by touching them electrically.
• a plurality of strip conductors, sections, arrangements and / or strip conductor networks intermesh.
• the number of printed conductor arrangements or interconnect networks is given by the number of measuring ranges and is given by the number of measuring ranges plus one.
• An adaptation of the properties is possible by adapting the conductor networks and / or - arrangements of the pressure sensor unit to the measurement requirements, which
• Adapting the distances of the interconnects and / or interconnect networks, arrangements and / or sections from each other, the width of the interconnects and / or interconnect networks, arrangements and / or sections to one another and the area coverage of the interconnects and / or interconnect networks, arrangements and / or sections is possible. Furthermore, an adjustment can be made by targeted painting of individual areas.
• Polymer layer are inserted. This further polymer layer is not conductive.
• the non-conductive polymer layer is provided with holes, stripes or other omissions. Now the area proportion and the exact extent of the omissions are varied until the desired measuring range is found. This is especially advantageous since this additional polymer layer is cost-effective for one and on the other hand can be quickly replaced.
• a coating corresponding to the non-conductive polymer layer is used during the production of the sensors.
• the relationship between pressurization and conductance and / or reciprocal value of the resistance value of the pressure sensor unit is in particular linear, in particular in each of the measuring ranges.
• the challenge is to find a layout of the tracks and / or sections, where each of the individual track networks covers each point of the area and there is also a distance between the networks. This is not possible. A closest approximation is preferred.
• the distance between the track networks determines the printing resolution of the
• the coverage of the area by each of the individual track networks determines the accuracy of the sensor. If the polymer is pressed onto the printed conductors, the polymer first of all touches a point. Are at this point only the tracks of a conductor network available there is no electrical contact between the different interconnects and the
• the mode of operation of a polymer pressure sensor is based on the fact that the resistance-conductive and / or conductive polymer is more or less pressed against the printed conductors depending on the load and thus produces a (resistive) electrical contact between two printed conductor networks. Depending on the load of the sensor, the electrical resistance and conductance varies.
• the tracks can be varied in width and arrangement, so that there is a different area coverage with tracks.
• a paint can be applied. This coating covers different areas of the tracks.
• Another possibility of painting is the partial coating of the surface on which the tracks are to cover the traces partially.
• the maximum measuring range increases.
• a hemispherical or spherical cap-shaped polymer If this polymer is pressed onto the printed conductors, the contact surface increases with the loading. The area increases concentrically with increasing load. The larger the area, the better the electrical contact and thus the measured value.
• a suitable finish can also be used to increase the life expectancy of a sensor.
• the conventional production of printed circuit boards does not result in an ideally smooth surface, but the printed conductors stand out.
• the height of such tracks is typically 35 or 50 ⁇ other heights can also be produced, however, a height of ⁇ is not displayed. If the sensor is loaded, the printed conductors are just pushing into the polymer. This leads to an increased
• a coating can be applied between the printed conductors and / or be corresponding to the negative of the printed conductor networks and / or printed conductors.
• today's painting methods are not absolutely accurate, there may be a slight shift in the pressure and the location at which this fills the gaps.
• This first coating is relatively thick, in particular by 10 to 30% and / or 3 to ⁇ lower than the conductor tracks, for example, in conductor tracks with the height of 35 ⁇ the coating is for example 30 ⁇ thick.
• a second coating is applied, which is thinner than the first, in particular 2 to 20 ⁇ thick.
• This coating is slightly larger and / or wider than the space between the interconnects and / or as the negative of the interconnect networks and / or Tracks, so that even with a shift, the tracks are (partially) partially covered.
• the or a first coat of paint in particular fills the spaces between the tracks coarsely, the second coating ensures the smoothest possible transition from trace to painted space.
• conductive layers and / or conductor track networks and / or sections which are embodied in particular, as in the case of an SRS, VRS and / or FSR sensor, has the pressure sensor unit, which is designed in particular as an SRS, VRS and / or FSR sensor , in particular one, in particular elastic, device for the targeted transfer and / or distribution of the pressure and / or a functional polymer.
• the functional polymer has at least one conductive surface portion, which may for example be part of the functional polymer or be present as a coating. As a rule, however, it is formed from a plurality of materials, in particular polymers, having different properties.
• the functional polymer has in particular a design or is designed as such. It can thus be the design, also called moldings represent.
• the design or the form body in particular has a non-continuous thickness over its cross section. She / he is in particular spherical and / or executed as a ball section and / or elastic.
• Cardiac output and / or and or the cardiac output means that the sensor is used on the skin and that forces in the range 1 -10N occur.
• a high data acquisition rate of at least 1000 values per second should be possible.
• silicone is used as polymer and / or functional polymer, in particular a plurality of silicones with different properties.
• the requirement of the measurement range and the high data acquisition rate mean that the functional polymer should exert a certain counterforce in order to react to a force change.
• the Shore hardness of the silicone can be adjusted, on the other hand, the design can be chosen in their geometric training suitable to allow the required counterforce.
• the functional polymer can also be made with a location-dependent variable Shore hardness. This is done in particular by the functional polymer, for example Layer by layer is applied and from layer to layer a different Shore hardness is used.
• variable Shore hardness is the use of special UV-curable polymers. These polymers change their Shore hardness when exposed to UV light. Depending on the exposure time, a Shore hardness can be set. Thus, e.g. Also different Shore hardnesses can be arranged concentrically by either masks are used or UV laser light is performed accordingly. In use, such UV-based polymer-based sensors must be constructed so that no light is applied to the polymer to maintain the Shore hardness.
• the form of the functional polymer in particular the design, represents a further adjustment variable.
• the task of the functional polymer is in particular at
• the functional polymer and / or the construction will have a layer of resistance-conductive polymer, in particular if the polymers otherwise used are not conductive.
• Resistive conductive and / or conductive polymer is available as a color and can be adjusted by the addition of other polymer inks in its conductivity.
• Resistive conductive and / or conductive polymer has in particular a resistivity between 0.2 and 10k ohms / cm / mm A 2.
• the intrinsic conductivity and the contact conductivity to the printed conductors are generally important. In most cases adjustment of the and / or the intrinsic conductivity is less important, since usually the distance between two tracks is less than 1 mm. More important is usually the
• the task of the functional polymer is, in particular, the conductive polymer of the
• the feet are designed in such a way that they provide the conductor tracks and / or conductive layers in a rest position of the pressure sensor unit for the separation of the functional polymer.
• the counterforce should be chosen so that the sensor can react sufficiently quickly to a pressure change by the variable pressure wave starting from the heart pulse in the arteries, ie a temporal mapping especially with an error less than 10%, in particular based on the duration of a pulse wave and / or in particular of less than 2 ms, in particular of 1 ms or less, and / or an error in the amplitude of less than 10%, in particular the maximum measurable amplitude and / or the maximum amplitude caused by the pulse wave.
• the spacers, for the functional polymer for the design and / or the spherical cap with a Shore A hardness, in particular according to ASTM D2240 (2015-08) and in particular test time of 1 second, between 85 and 98, in particular when arranged on strip conductors and / or for the electrical connection of printed conductors between 90 and 98, in particular between 92 and 97, in particular between 94 and 96, in particular of 95 and / or in the arrangement between conductive layers and / of the printed conductors (in particular as below describe as an alternative embodiment of the pressure sensor unit) between 85 and 95, in particular between 88 and 92, in particular 90 and / or a size, in particular maximum size, of the functional polymer, in particular in cross section parallel to the planar extent of the conductor tracks and / or conductive layers , between 1 cm x 1 cm and 2 cm x 2 cm and / or a height between 0.5 and
• spacers for the functional polymer, for the design and / or the ball cap, the use of silicone has proven particularly useful.
• spacers, in particular feet, and ball cap are integrally formed, in particular together with a connecting portion for connecting spacers and ball cap, and in particular has the ball cap on a conductive coating.
• the functional polymer has a design which has a shape of a spherical cap or a segment of a sphere, the spherical cap or the segment in particular having a maximum diameter between 2 and 9 mm, in particular between 4 and 6 mm and / or a height between 0.5 and 3 mm, in particular between 1 and 2 mm and in particular a cap or a segment of a ball with a diameter between 8 and 30 mm.
• the spherical cap or the segment in particular having a maximum diameter between 2 and 9 mm, in particular between 4 and 6 mm and / or a height between 0.5 and 3 mm, in particular between 1 and 2 mm and in particular a cap or a segment of a ball with a diameter between 8 and 30 mm.
• the spherical cap or the segment in particular having a maximum diameter between 2 and 9 mm, in particular between 4 and 6 mm and / or a height between 0.5 and 3 mm, in particular between 1 and 2 mm and in particular
• Ball cap and or the segment of a coating of conductive polymer are made of silicone.
• functional polymer of the design and / or spherical cap are made of silicone.
• feet are arranged laterally next to the ball cap and / or the segment.
• conductor tracks, feet, functional polymer, conductive coating and / or design are designed and arranged such that at rest between functional polymer, in particular conductive coating on the ball cap, and conductor tracks a distance between 0.05 and 0.5 mm, in particular between 0.05 and 0.2 mm.
• Smaller functional polymers should have a softer polymer or smaller overall area of the spacers to allow for desired strain, but a softer polymer will follow the pulse wave more poorly due to the lower recovery capability.
• the polymer of the design and / or the design in particular of a resistive conductive and / or conductive polymer, in particular a resistive conductive and / or conductive coating, has the task to one to lead the sensor at no load in a defined initial state, the other is a defined reset pressure built up.
• This reset pressure is useful to suppress mechanical trembling, which in turn can lead to a noise of the measured values.
• the functional polymer in particular resistance-conductive and / or conductive polymer, in particular a resistance-conductive and / or conductive coating, has the task of controlling the contact surface of the resistance-conductive and / or conductive polymer to the interconnects.
• the functional polymer, in particular resistance-conductive and / or conductive polymer, in particular a resistance-conductive and / or conductive coating, should be distinguished in particular by the fact that it is a very fast
• the functional polymer in particular resistance-conductive and / or conductive polymer, in particular a resistance-conductive and / or conductive coating
• the mechanical properties of the functional polymer, in particular resistance-conductive and / or conductive polymer, in particular a resistance-conductive and / or conductive coating should also be adjusted so that no lasting impression of the conductor tracks can form in the polymer, even with frequent exposure of the sensor up to the maximum pressure range.
• the resistance-conductive and / or conductive polymer establishes the contact between the individual interconnects. Its properties are in particular that it actually, ie in the idle state of the pressure sensor unit, does not have good contact with a conductor track. This is given in particular by the fact that the microstructure of the surface of the polymer, in particular of the resistance-conductive and / or conductive surface, is very uneven.
• the functional polymer and / or the construction has in particular at least one spacer and / or foot, which is in particular furnished, the functional polymer, in particular the resistance-conductive and / or conductive polymer, in particular a resistance-conductive and / or conductive coating in a quiescent state or unloaded state of the pressure sensor unit of the conductor tracks, conductor track assemblies and / or networks to keep so far that there is no electrical contact.
• Feet for example, can be configured as individual elevations or concentric structures. They may be adapted in shape and proximity to the functional polymer, in particular to the resistance-conductive and / or conductive polymer, in particular to the resistance-conductive and / or conductive coating, in such a way that the desired counterforce of the sensor is achieved.
• the functional polymer in particular the resistance-conductive and / or conductive polymer, in particular the resistance-conductive and / or conductive
• Bump, spacers and / or feet can have a different Shore hardness or the same Shore hardness as the remaining functional polymer and / or the rest of the design.
• feet can take over the task of holding the polymer in position, so that ideally no lateral movement of the polymer takes place via the conductor tracks in the event of a shear stress on the sensor.
• the at least one spacer is in particular with a carrier on which the conductor tracks are arranged and / or glued to a conductive layer, in particular in holes or depressions of the carrier.
• the positions and shape of the feet should be chosen appropriately. A few small feet will result in an uneven stress field on the functional polymer under load. The functional polymer does not thereby deform concentrically to the applied
• This ring has two main parameters:
• the thickness or width of the ring determines how much force the sensor can absorb until it is squeezed out.
• the thickness should be selected such that the linear range between the application and the measured value is as linear as possible in the targeted measuring range.
• the height of the ring determines from which force the sensor delivers a signal. So that an optimal and well-resolved measurement can take place, the height should be selected so that a measurement takes place only after a meaningful admission.
• a further resistance-conductive and / or conductive polymer is applied to the functional polymer and / or the construction, if the remaining functional polymer and / or the remaining construction is not resistance-conductive or conductive, and / or has the functional polymer and / or the construction when the remainder of the functional polymer and / or the remainder of the construction is non-resistive or conductive, a resistive conductive and / or conductive polymer.
• the size of the functional polymer depends in particular on the area of the interconnect networks.
• An alternative pressure sensor unit includes a plurality of sensitive active surfaces or volumes one above the other and / or into each other. For example, several measuring ranges can be created that can be used simultaneously at the same measuring point.
• Contact pressure changes the electrical contact between the metal tracks and the polymer.
• the polymer produces a resistive contact between the two tracks.
• the resistance results from the sum of the contact resistances between the polymer and the two interconnect networks and the resistance of the polymer per se.
• An alternative pressure sensor unit includes two surfaces or layers of conductive
• the Shore hardness of the conductive and the non-conductive polymer is selected so that in the desired measuring range at a loading deformation can take place.
• the shape of the surfaces or layers need not be even, but can be adapted to the measuring system or to the measuring task.
• the sensitive surface is advantageously on the surface of this finger berry shape and therefore curved.
• the design of the non-conductive surface or layer is crucial for the possible measurable measuring range.
• At least one hole, in particular holes, in the non-suffering layer, for example, non-conductive polymer or non-conductive paint is introduced and / or provided, whereby at least one air-filled cavities formed.
• the non-conductive layer or surface deforms or the three surfaces or layers deform and the upper and lower surfaces or layers of conductive polymer contact each other.
• the result is a resistive electrical contact.
• the contact surface and the contact pressure of the surfaces become stronger and there is contact in more and more cavities and / or on larger surfaces. This reduces or increases the electrical resistance
• An improved structure of the cavities between the conductive polymers can be achieved by increasing the maximum contact area per cavity or hole or in total.
• at least one hole is introduced into the non-conductive surface or layer as usual, and in addition conductive material, in particular polymer, is arranged in the at least one hole or in the holes in order to produce extensions of the conductive layer into the holes.
• one or both conductive layers, in particular with at least one extension protrude into at least one hole, in particular in such a way that no contact is made between the conductive layers in the at least one hole or in the holes at rest.
• the arrangement or extensions may in particular be hemispherical and / or spherical cap-shaped and / or as a negative shape and / or on the lower conductive surface in a first shape and a counterpart complementary to the first shape and / or approximately complementary counterpart on the upper surface. So it works
• the adjustment of the force range of such an arrangement can be achieved, for example, by the number of cavities and the shape of the arrangement of conductive polymer in the
• Cavities is changed.
• the size and shape of a cavity is a parameter, as well as the number of cavities per unit area.
• the thickness of the surfaces and their hardness, in particular the non-conductive surface, are further adjustment parameters.
• the 3D printing also allows further possibilities of mechanical adjustment of the sensors for setting a measuring range.
• the insulating polymer and / or the insulating paint at rest in particular a thickness between 0.5 and 2 mm and / or exists between the conductive
• the conductive layers and / or the insulating polymer and / or the insulating lacquer have a planar extent of between 0.5 cm ' 2 and 9 cm ' 2, in particular between 1 cm * 2 and 5 cm ' 2.
• the insulating polymer and / or the insulating varnish 3 to 15 holes and / or holes with a total area of 50 and 200mm A 2, in particular per lcm A 2 to 5cm A 2 total area of the insulating polymer or varnish, and / or have the holes an area of 10 to 40 mm A 2 each.
• the hardness of the non-conductive layer has a Shore A hardness, in particular according to ASTM D2240 (2015-08) and in particular test time of 1 second, between 85 and 98, between 85 and 95, in particular between 88 and 92, in particular of 90 , proved beneficial. It is formed in particular of silicone.
• the cavities or holes described above contain air, which usually can not escape, thus increases with the application of pressure in these cavities.
• This phenomenon can either be remedied by creating or incorporating an orifice that allows pressure equalization, for example connecting the cavity to the outside world, or this phenomenon can be used as a dynamic adjustment parameter of the sensor in the application.
• a pressure can be generated in these cavities with a pump, whereby the deformability of the cavities can be changed.
• the measuring range is adjustable with the pressure in the cavities.
• three surfaces of conductive polymer, separated from two surfaces of non-conductive polymer, are required.
• the parameters of the structure of the cavities between the first two conductive surfaces are set and / or adjusted differently from the parameters of the structure of the cavities between the second and third conductive surfaces.
• Another possibility of arranging a plurality of measuring ranges within a sensor can be carried out by using only two surfaces of conductive polymer. However, one or both surfaces are constructed of stripes. These strips are in turn separated by non-conducting polymer. Each strip is assigned to a measuring range, with two measuring ranges, the assignment on a surface is in particular designed alternately. The mating strips are electrically connected outside the sensor. The cavities are now adapted for each group of stripes, ie for the corresponding measuring ranges in their parameters and / or are designed differently.
• Resistance between any pairs of strips, consisting of a strip on each surface, can be determined.
• the place of greatest stress is the intersection of the pair with the least resistance.
• Integration of a sensor or several sensors in the housing or fastening elements of a wearables can be optimally adapted to the measuring task with the aid of 3D printing and can be equipped with functionality.
• 3D printing allows the integration of a press system, which e.g. based on 3D printed pneumatic components, or the integration of further sensors, such as e.g. Sensors for
• Air cuffs with pneumatic air pressure sensors for measuring blood pressure according to the Riva Rocci method are a separate necessary development for an arrangement for collecting vital data.
• the definition of the parameter cardiac output of the cardiovascular system is possible in particular if initially other parameters, such as blood pressure and cardiac output are defined. Therefore, in the following, all parameters that can be measured with an arrangement according to the invention are defined and, lastly, the cardiac output.
• the blood pressure at different points of a human or animal body is also visible to the human eye now and then.
• the blood pressure from the heart thus not only felt in the periphery of the human or animal, but also visible.
• the pulsation is produced by the temporal change in pressure at each individual heartbeat.
• the pulse wave (see Fig. 1 letter D) is also generated. This can be registered peripherally as the first reaction of a successful heartbeat.
• the Windkessel absorbs a portion of the blood volume and releases this portion within a RR interval until complete emptying, measurable as diastole.
• the pressure pulse or the current pulse can be registered.
• Riva Rocci method To measure blood pressure non-invasively, the Riva Rocci method has been used for over 100 years.
• the method works by squeezing the artery with the aid of an inflatable air bag. Then one dissolves controlled and measurable the uniform
• Method uses tapping for blood pressure determination.
• the arrangement according to the invention makes use of this event by using sensors with corresponding temporal resolution and with the lowest possible attenuation.
• the invention uses the incoming pressure / pressure propagation direction to the surface of the human skin (see Fig. 1 letter N), here, for example, at the A. Radialis.
• the pulsating pressure from the arterial wall propagates across the tissue (see Fig. 1 C) to the surface of the skin (see Fig. 1 Letter O). There, the pulsating pressure / blood pressure, but already damped, through the tissue by means of sensory and processing unit registered (see Fig. 1 letter K and H) are.
• the directly measurable pulse pressure has been a proven remedy for medical professionals for centuries, not only in the field of accident care.
• the type of pulse pressure propagation, Fig. 1 letter N, and the speed of the pulse, Fig. 1 letter M, can give inferences about the constitution of the measuring person based on the sensed pulse statement.
• the registerable pressure increase is used directly in the invention as a cause for blood pressure measurement.
• the pulsating pressure pulse deforms the artery, Fig. 1 letter E, constantly in time with the beating heart, Fig. 1 letter G.
• the pressure pulse is changed by branching, states of the vessels, as well as the external and internal load.
• the blood pressure reading is a constantly adapting value to the particular situation of the body.
• the mode of operation of the heart is controlled by the sinus node, which indicates the rhythm with which the heart contracts, which causes the blood to be ejected first into the air chamber and then into the arteries.
• the sinus node stimulates the muscles of the heart by electrical signals.
• a full cycle of expectoration of the blood into the arteries and aspiration process from the veins is a cardiac pulse.
• the electrical signals of the sinus node are recorded in the conventional method for measuring heart rate with an electrocardiogram (ECG).
• ECG electrocardiogram
• Atrial flutter and atrial fibrillation An example of this is atrial flutter and atrial fibrillation.
• the contraction in the atria is triggered by up to 340 (atrial flutter) or up to 600 (atrial fibrillation) contractions per minute by electrical signals.
• heart chambers usually open irregularly with 100-160 orifices per minute. This condition is called absolute arrhythmia.
• the arrangement according to the invention determines measured values which map the pulsating pressure wave.
• the pulsating pressure wave in the arteries comes about only when it comes to a blood discharge from the heart.
• an unambiguous measurement of the cardiac pulse is possible via the analysis of the measured values which map the pulsating pressure wave.
• the pulse wave variability also called heart rate variability, indicates the variability of the cardiac pulse. High variability is a sign of a healthy heart.
• the heart pulse adapts autonomously to the requirements of the organism and is therefore inferior to a constant change. If the person to be examined is, for example, under increased stress, the result may be an even cardiac output.
• the arrangement according to the invention permits the time intervals between each individual heart pulse to be determined. These intervals are called RR intervals.
• the pulse wave variability can be expressed as the standard deviation to the mean of the RR intervals.
• Pulse wave transit time and pulse wave velocity are two closely related characteristics of the cardiovascular system.
• the pulse wave transit time indicates the time in which the pulse wave has traveled a certain distance and the pulse wave velocity combines the pulse wave transit time and the distance traveled. Therefore, from the knowledge of the distance traveled, the two parameters can be converted into each other.
• the pulse wave velocity must not be confused with the speed of the blood in the arteries, this is much slower.
• a pressure pulse sets in the arteries in motion, this deforms the arterial walls. In turn, this means that the pressure pulse can only move as fast as the arterial walls can deform.
• Deformability is the elasticity of the arteries.
• the elasticity of the arteries can be determined by measuring the pulse wave velocity.
• the skilled person may, inter alia, use the Moens-Korteweg formula and / or the Bramwell & Hill formula which determines the dependence of the Pulse wave velocity of elasticity, arterial wall thickness, arterial diameter and blood density
• the value of elasticity is regulated by the cardiovascular system.
• the elasticity may e.g. be excessively reduced by arteriosclerosis. Therefore, the elasticity is a characteristic, e.g. warn of impending heart attacks.
• Pulse wave velocity can also be used to monitor the blood pressure.
• the pulsating pressure wave can be measured with several sensors at different points of the body.
• the pulse wave transit time can be determined from the offset of the measured curves relative to one another, whereby, knowing the distance of the sensors from one another, the pulse wave velocity is also known.
• the sensors can also be close to each other. This allows the measurement of
• the pulsating pressure wave of the heart pulse is also reflected. Due to the high data acquisition rate of the inventive arrangement, the reflection wave is recognizable in the measurement curves.
• the pulse wave transit time can also be calculated from the distance between the initial wave and the reflection wave.
• the cardiac output indicates how many liters of blood the heart expels in one minute and is available for the care of the organism. Thus, this characteristic or its change represents the quantity for assessing the performance of the cardiovascular system.
• a normal reduced value is an indication of heart disease, e.g. heart valve disease or an indication of hypothyroidism.
• Normal elevated levels may be due to a variety of diseases, e.g. Fever, anemia or circulatory disorders of organs.
• Cardiac output is also an indicator of oxygen supply to the body.
• a high cardiac output (as long as it is not disease-related) is desirable and can serve as a measure of specific, performance-oriented training measures.
• One method that is often used involves injecting a cold fluid with a catheter into a chamber of the heart. By means of temperature sensors in the arteries following the heart, the heating can be determined; this heating is directly related to the cardiac output.
• An inventive arrangement is intended to provide an alternative to the invasive methods, which, for one, does not interfere with the body and thus no dangerous operations needed and the other as accurate as possible measurement of cardiac output or its change allows. Therefore, the location between the medically very precise and necessary examination situations in complicated and long operations and the very inaccurate previous non-invasive methods. Therefore, in operations that do not require the utmost exact value, an invasive method can be dispensed with and an inventive arrangement can be used instead. Since the attachment of an inventive arrangement is quick and easy, it is also possible to monitor during operations in which no cardiac output monitoring has hitherto been used. In addition, especially in the medical field, new possibilities arise, so a continuous long-term monitoring can be made possible and in case of deterioration an alarm can be issued.
• the determination of the value for the current cardiac output can be from cardiac pulse to cardiac pulse.
• the parameters of heart rate or RR interval, pulsatile pressure wave curve, arterial elasticity and aortic arch diastolic blood pressure are all determined.
• An inventive arrangement can measure the cardiac output at least approximately relative to the diameter and / or cross-sectional area of the aortic arch in diastolic blood pressure, and if desired, this relative value can be converted to an absolute value by an external measurement of the diameter of the aortic arch in diastolic blood pressure.
• the pulse wave passes from the heart into the arteries, while the amplitude decreases and the individual pulses are longer in time.
• the output pressure wave must traverse all arteries and the total pressure as integrating over time, in particular a pulse wave, an RR interval and / or between two systolic pressures or two diastolic pressures, at a certain distance from the heart is approximately equal to that
• Ejection pressure which is related to cardiac output and elasticity.
• the elasticity in turn can also be determined at least approximately and used for further improvement as a correction of the at least relative cardiac output.
• the ejection volume of a cardiac pulse even without further correction by the elasticity can be approximately determined as follows:
• pulse pressure is the pressure difference between the diastolic blood pressure value and the current measured value
• the radius R is given by the elasticity E :
• the current radius of the artery changes during a cardiac pule with the time pressure.
• the length L of the artery deformation in a cardiac pulse must be determined.
• the temporal length of a cardiac pulse, the RR interval T , and the pulse wave velocity v are linked:
• an invasive method can be dispensed with and an inventive arrangement can be used instead. Since the attachment of an inventive arrangement is quick and easy, it is also possible to monitor during operations in which no cardiac output monitoring has hitherto been used. In addition, especially in the medical field, new possibilities arise, so a continuous long-term monitoring can be made possible and in case of deterioration an alarm can be issued.
• the determination of the value for the current cardiac output may vary from cardiac pulse
• Heart pulse done. The parameters of heart rate or RR interval, pulsatile pressure wave curve, arterial elasticity and aortic arch diastolic blood pressure are all determined.
• An inventive arrangement can measure the cardiac output at least approximately relative to the diameter and / or cross-sectional area of the aortic arch in diastolic blood pressure, and if desired, this relative value can be converted to an absolute value by an external measurement of the diameter of the aortic arch in diastolic blood pressure.
• the pulse wave passes from the heart into the arteries, while the amplitude decreases and the individual pulses are longer in time.
• the output pressure wave must traverse all arteries and the total pressure as integrating over time, in particular a pulse wave, an RR interval and / or between two systolic pressures or two diastolic pressures, at a certain distance from the heart is approximately equal to that
• Ejection pressure which is related to cardiac output and elasticity.
• the elasticity in turn can also be determined at least approximately and used for further improvement as a correction of the at least relative cardiac output.
• the ejection volume of a cardiac pulse even without further correction by the elasticity can be approximately determined as follows:
• the present pulse pressure ⁇ " (pulse pressure is the pressure difference between the diastolic blood pressure value and the current measured value) in an artery deforms this, the radius R is given by the elasticity F -:
• R o is the (unknown and externally measured) radius of the artery.
• the current radius of the artery changes during a cardiac pule with the time pressure.
• the length L of the artery deformation in a cardiac pulse must be determined.
• the temporal length of a cardiac pulse, the RR interval T , and the pulse wave velocity v are linked:
• K o For a relative measurement K o is set to zero, if an external measurement has taken place can be transmitted as a parameter to the inventive arrangement.
• a pressure sensor unit as already described above, can be applied to the skin, FIG. 1
• a wristband Fig. 1 (I)
• a uniform pressure Fig. 1 letter J
• Fig. 1 letter J can be exerted on the A. radialis.
• the outgoing pressure transferred from the A. radialis to the surface of the skin can already be registered with a simple measurement setup of a pressure sensor unit between the bracelet and the surface of the skin.
• the dynamic pressure pulse of the actual ejection of the heart can be made so visible to everyone by means of the evaluation and imaging unit.
• the arrangement according to the invention has an invaluable value for patients who are invasively connected to a monitor, for example, in the intensive care unit, since the measurement does not have to be performed invasively, as is usual today.
• Measuring points such as the artery Dorsalis pedis, anterior tibial, Posterior tibiels, as well as First dorsal metarsal, Deep plantar, Arcuate are suitable for measurement on the back of the foot.
• the total amount of inflowing bloodstream changes the diameter of the lower limb.
• a limited usability of the invention also exists in diseased people, for example. By strong water deposits in the legs and especially in the feet.
• the required back pressure and / or contact pressure can be generated, for example, by means of a finger (see Fig. 1 letter J) of the other free hand.
• a specially prepared and clearly defined for the user surface on the bracelet or system can be created.
• R o For a relative measurement R o is set to zero, if an external measurement has taken place R o can be transmitted as a parameter to the inventive arrangement.
• a pressure sensor unit as already described above, can be applied to the skin, FIG. 1
• a wristband Fig. 1 (I)
• Fig. 1 (I) can be used around the wrist as an aid and as a commercial product.
• the outgoing pressure which is transferred from the A. radialis to the surface of the skin, can already with a simple measuring structure of a pressure sensor unit between
• the dynamic pressure pulse of the actual ejection of the heart can by means of
• inventive arrangement an invaluable value for patients who are invasively connected to a monitor, eg. In the intensive care unit, since not as usual today, the measurement must be performed invasive.
• the measurement of blood pressure can be greatly influenced by the surrounding tissue.
• An advantageous measuring point is at the upper instep, since there is usually little fat stored here.
• Measuring points such as the artery Dorsalis pedis, anterior tibial, Posterior tibiels, as well as First dorsal metarsal, Deep plantar, Arcuate are suitable for measurement on the back of the foot. In the area above the ankle, the total amount of inflowing bloodstream changes
• Diameter of the lower extremity With a measurement of the variable diameter or the variable pressure on the applied measuring surface with at least one
• Pressure sensor unit is also here to detect the blood pressure and heart rate.
• a limited usability of the invention is also in diseased
• the required back pressure and / or contact pressure can be generated, for example, by means of a finger (see Fig. 1 letter J) of the other free hand.
• a specially prepared and clearly defined for the user surface on the bracelet or system can be created. This surface 32
• the pressure sensor unit is located above the at least one pressure sensor unit and thus, for example, on the bracelet. Directly below the pressure sensor unit is, for example, the A. Radialis.
• the user can, for example, a finger on the defined
• the back pressure on the artery or pulse wave should be guided beyond the attenuation.
• the systole becomes measurable at the moment the back pressure and / or contact pressure continues to increase, but the pulse wave can not produce a maximum increase beyond the maximum measured pressure.
• the invention can easily be tested on humans themselves. Before squeezing the A. Radialis completely with the increasing pressure on the radialis, there is a pressure range in that, despite an increase in the back pressure, the pulse pressure does not noticeably increase any further.
• This point can be measured by known devices and represents the systole of the blood pressure.
• the diastole is determined from the minima of the pulsating pressure wave. As the back pressure on the artery increases, the distance between the minimum and maximum of the pulsating pressure wave initially increases, with the maximum pressure also increasing. From a certain backpressure the maximum measured pressure does not increase any further. This is just the back pressure that corresponds to the diastolic blood pressure.
• a one-time measurement can therefore be carried out by slowly increasing the back pressure on the artery until no increase in the maximums in the pulsating pressure wave can be detected.
• the continuous measurement is carried out in the same way in the first instance. In particular, however, at the point where no increase in the maxima can be seen, remains. If the systolic blood pressure changes, this can be detected by a change in the maxima of the pulsating pressure wave. Now, the back pressure should be adjusted again to determine the new value for the blood pressure, in particular starting from a value below the systolic blood pressure, be increased again until an increase of the maxima is no longer present.
• pressure sensor units are attached to at least two suitable measuring points and pressed by an actuator or manually with the back pressure and / or contact pressure to the skin, in particular with the optimum measuring pressure of the continuous measurement, and / or the back pressure and / or contact pressure in the area, between the pressure of the pulse wave in the diastole or the determined diastolic and the pressure of the pulse wave in the systole or the determined systolic blood pressure and / or up to 1, 5-fold, in particular 1, 3-fold, the pressure of the pulse wave in the systole and / or the systolic blood pressure and / or from 60 to 120 mmHg, in particular from 60 to 90% of the systolic pressure of the pulse wave in the systole, in particular at the place of measurement and / or as low a pressure as possible, but sufficient to image the pul
• Pulse wave delay and the pulse wave velocity can now be done automatically.
• the multiple measurement of the current blood pressure at each measuring point allows to show the course of the blood pressure between diastole and systole in each individual pulse. This is particularly advantageous for assessing the cardiovascular system. For example. can the
• Reflection wave can be detected. If this is, for example, increased in relation to the initials pulse or pressure wave, this indicates a vascular stiffness.
• the examination of the reflection wave represents a possibility to determine the elasticity of the arteries.
• the measurement of blood pressure can also be measured at less than 1000 measurements per second.
• the invention also provides the solution to generate the back pressure and / or contact pressure by means of actuator.
• the advantage consists in the uniform increase of the acting back pressure and / or contact pressure, in particular on the artery.
• the advantage of using an actuator is also the timely cancellation of the measurement, or the limitation of the back pressure and / or contact pressure, in particular on the artery, before or so that the back pressure and / or the contact pressure squeezes the artery.
• the blood pressure measurement can be done automatically, for example, during the night and gently.
• An actuator has in particular an airbag and a pump for pressurizing the airbag.
• a limb is enclosed by an elastic or non-elastic, enclosing device, for example a band, and an airbag is arranged between the band and the skin or on the inside of the band between the pressure sensor unit and the encircling device.
• the air bag is subjected to the generation of the contact pressure in particular with pressure, in particular by pumping in gas, in particular air.
• a hydraulic or pneumatic actuator has one or more of the following components: pipes, lines, check valve, pump, drain valve, closing valve,
• Pressure relief valve buffer volume and / or actuators.
• measuring techniques can be applied at the location of the pressure sensor unit.
• measuring techniques can be integrated that record location-independent values
• Measurement techniques that can be used at the location of the pressure sensor unit are:
• Plethysmography, ECG, pneumatic pressure measurement and / or tone detection Plethysmography, ECG, pneumatic pressure measurement and / or tone detection.
• Measuring techniques that can be integrated are: acceleration sensor, gyroscope and / or recording of environmental parameters.
• the system or method or use may also be designed so that the pressing is also arranged to completely block the artery. This allows the measurement of blood pressure according to the conventional method, the Riva Rocci method, by means of tone detection.
• a Riva Rocci measurement is achieved by using either a sensor to detect sounds, e.g. a microphone, a sensor, for example a pressure sensor unit according to the invention, is used and / or contained for pressure measurement in a pneumatic pressure system, for example an airbag and / or a sensor for plethysmography.
• a sensor to detect sounds e.g. a microphone
• a sensor for example a pressure sensor unit according to the invention
• the arteries are squeezed in the arm and slowly released again. If the arm is relieved, the arteries open at a certain level of stress, which is the systolic value of blood pressure. When the arteries are fully opened, the blood flows back to normal. The maximum contact pressure at which normal blood flow is still possible is the diastolic value of the blood pressure. This is measured by examining the sounds of the flowing blood. Are the arteries squeezed off no noise is present. When the arteries are partially open, there is a rushing and poking sound. In normal blood flow no noise is heard. In today's automated systems, a method is also used which analyzes the pressure in the arm cuff. If the arm is squeezed, the pressure in the cuff is stable over time. When the arteries are partially open, there are strong rashes. When the arteries are completely open, there are no or very small measurable rashes in the pressure measurement curve.
• the entire arm does not have to be squeezed off. If, for example, a bracelet is used, only the A. radialis must be squeezed off, it can be confined to a smaller area. If a microphone is embedded in the combined sensor, the sounds are analyzed as in the conventional method. It is also possible to use the pressure of the pressing system for the measurement. The blood pressure values obtained in this way are accurate to the levels that can be measured with a conventional blood pressure cuff. 35
• Plethysmography measures the cardiac pulse by radiating light into the tissue and analyzing the intensity of the reflected light. Depending on the blood filling in the arteries, the light intensity is different and, since the blood filling varies within a heart pulse, the heart pulse is measurable. In particular, plethysmographic sensor is placed farther from the heart than the pressure sensor unit.
• the unit of plethysmography When using a bracelet, the unit of plethysmography is placed closer to the hand than the point where the A. radialis is squeezed off with the pressure system. If the A. Radialis is squeezed, no fluctuation in the light intensity is measurable.
• the artery opens it causes measurable changes in light intensity and the artery is loaded with systolic pressure. With increasing opening of the artery, the intensity fluctuation increases. With stresses on the artery which are smaller than the diastolic value, the intensity fluctuation no longer increases.
• the accuracy is higher than in the conventional Riva Rocci method, as the actual blood flow is examined and not an indirect noise or a pressure fluctuation in the pressing system. Therefore, such a combination of sensors is particularly suitable for applications in heavy movements.
• the pressure sensor unit is provided with an electrode which is pressed onto the skin. So that a signal can be detected, a second electrode is applied to the surface of the measuring system. The user can now measure his ECG wave by using the s.g. Cabrera circle closes and with the other hand touches this outer contact.
• the ECG wave is examined for heart rate by determining the times of each pulse.
• the times of the pulses correspond to actions of the heart. So the time of blood ejection from the heart can be determined.
• the time can be determined at which the pressure wave is due to the blood ejection, at the measuring point. The time difference of these times is the pulse wave transit time or (with knowledge of the distance between heart and measuring point) the pulse wave velocity can be calculated.
• a system according to the invention comprises a enclosing device, in particular a band, and at least one
• the enclosing device can also by a shoe, in particular with
• Locking system are formed.
• the system may also include a shoe with locking system with actuator and at least one pressure sensor unit in the shoe.
• the actuator for generating the backpressure and / or contact pressure may, for example, be a conventional electric vibration motor produced in SMD construction. But also any other actuators can satisfy the build up of the back pressure.
• the actuator also has the disadvantage that electrical energy is consumed. This must be calculated in the respective application.
• the measurement can be made by one person without the help of a finger of the other hand, or a third party, or even another actor.
• FIG. 3 shows a convex structure labeled with letter Q, as a carrier form of the system or sensor array.
• the arterial system is usually protected and secured inside the body. In the extremities often only the veins are clearly visible. The arterial circulation is deeper in the tissue. Only in a few places of the body can arteries be felt in a striking way through the pulsating wave.
• the convex structure Fig. 3 letter Q, is an inventive novelty.
• the convex structure nestles almost exactly in the concave forms of the body, such as the A. Radialis. Placing the convex structure on the concave shape that forms above the radial artery and towards the surface of the skin allows an optimal pulse wave to be registered and stored. The same applies, for example, also for the foot.
• foam or foam-like material between the flexible sensor unit and the Anpress stresses, eg. A convex structure.
• the foam similar to the tissue above the finger bone, serves as a resonator.
• the functional Shore hardness of the pressing body can be adapted to the tissue of a fingertip.
• the task can be solved with the aid of sliding glides on a bracelet, for example a watch strap, and also with the aid of straps.
• a bracelet for example a watch strap
• An even more accurate placement can be achieved by using multiple sensors, see below.
• a conventional watch band has at least one tab, Fig. 2 letter P, for the protruding perforated belt for optimum adjustment of the contact pressure of the clock on
• the protruding perforated tape and without insertion into the tab would turn away from the shape of the wrist and stick out.
• the attachment of the measuring unit is done in particular as follows:
• the measuring unit or system is pushed onto the bracelet with the opening, Fig. 3 (I), such as a tab (s), see Fig. 2 (P).
• the attachment of the measuring unit in a size of, for example, and about 10 x 20 x 8 mm, is guaranteed.
• bracelet is, for example., See Fig. 3 letter H, the arithmetic and radio unit and the power supply.
• the convex structure with the pressure sensor units is located below the bracelet. See Fig. 3 letter Q.
• the measuring unit or the system with the convex structure can measure the blood pressure in this construction with each already used bracelet. 37
• the inventive novelty is thus also in the variable usability of already existing bracelets for watches, jewelry or smart devices.
• the flap opening of the measuring unit can be made so wide that not only the convex structure on the bracelet can be moved around the wrist, but also with the tab, or within the tab, the convex structure including pressure sensor unit, to the hand, or moved away from the hand.
• the invention for example, to the surface of the skin, can be easily placed and serve as a mobile solution to measure the various characteristics of the cardiovascular system.
• the measuring unit is a part of the bracelet, or the tab, with such an arrangement for a bracelet and thus the measuring unit is already located at a suitable location for blood pressure measurement and on the other hand, by adjusting the perforated belt on a pressure the sensor be exercised.
• the measured value can be transferred to a mobile smart device.
• the optimal location and / or pressure sensor unit of a sensor array for registering the physical pulse wave can be determined. Also a display of the instruction for the shift, for example on a smart device, solves the task for the correct placement by means of arrow directions displayed on a screen.
• Pressure sensor units are distributed. Ideally, these pressure sensor units cover the entire surface of the convex structure. To measure the various parameters of the cardiovascular system, there are now several pressure sensor units to choose from, which in turn can have several (for example two) measuring ranges.
• the signal or the measured values and / or conductance values and / or resistances of all pressure sensor units are advantageously examined. These change over the course of a pulse wave.
• the optimally located pressure sensor unit and / or the pressure sensor units located optimally are characterized by the highest amplitude of the signal or the measured values and / or conductance and / or resistances.
• the optimally located or optimal pressure sensor unit (s) will be used for carrying out the (further) method, in particular for measuring the blood pressure, the arterial elasticity, the pulse wave, the pulse wave transit time and the
• Pulse wave velocity and / or changes in cardiac output and / or and or cardiac output used Pulse wave velocity and / or changes in cardiac output and / or and or cardiac output used.
• m is equal to 2 or greater.
• the system is set up so that the optimally lying or the optimally lying m
• Pressure sensor unit (s) are detected by the system, for example, by a comparison of m or the highest amplitude (n) of the signal by means of the evaluation, wherein when determined no or less than m highest amplitudes and / or upon detection of a variation of at least 80 %, in particular 90%, in particular all, amplitudes of less than 10%, in particular less than 5%, of the mean value of the amplitudes information 38
• a display of the instruction for the shift eg. On a smart device, for the correct placement, for. B. by means of arrow directions on a screen, is shown.
• the best measuring range is determined by the maximum value.
• Pressure sensor unit (s) can be transferred to an evaluation unit and to a picture or sound output by means of recording, computing power and transmission unit.
• the mobile solution such as a smart device, such as a clock or
• the system may be equipped with a rechargeable battery or a battery, it would also be advantageous to provide energy via a smart device, such as a clock or a
• the measuring sensor system can also be formed separately in the convex structure and access external units (rake, radio, etc.), for example a smart device.
• shutdown of data determinations from the pressure sensor units is preferred for a faster readout of the pressure sensor units by means of crossover circuits of electrical conductor tracks. whereby less data must be processed or read out.
• the measured blood pressure depends on the location of the measuring point to the HIP (hydrostatic indifferent point).
• HIP hydrostatic indifferent point
• Measurements on the foot usually produce only minor changes in the movement to the HIP.
• the height of the HIP should also be determined during physical exercise
• the measured blood pressure e.g. in the arm changes depending on the height above the HIP.
• the central blood pressure Pz in the HIP can be calculated:
• the height of the arm can be determined with different technologies or devices. Possible known methods are the determination of the distance to a
• Reference surface This can be done, for example, with an ultrasonic distance sensor or with a laser range sensor. These sensors send out a signal (sound or
• the length is determined from the transit time of the signal to the reference surface and back.
• the current height and / or the change in the height of the measuring point, the at least one pressure sensor unit and / or the system can also by the use of a
• Acceleration sensors, gyroscopes and / or inertial sensors are determined.
• the movement of the arm can be traced and the current location of the arm can be determined.
• the sequence of movements in each step should be accurately assessed to determine the correct height.
• the procedure for this is to set the measured acceleration data in comparison to the expected acceleration data.
• known motion patterns are compared with the current acceleration data.
• Match detected the movement can be determined to the current position.
• the current electrical resistance or conductance of a pressure sensor unit or a measuring range of an SRS sensor or the resistance of a VRS sensor can in the simplest case on the
• the pressure sensor unit carried out in a voltage divider.
• the voltage that drops across the pressure sensor unit is the output measurement signal that is directly related to conductance and / or resistance.
• the pressure sensor unit can alternatively or additionally be read in another way.
• the voltage which drops across the pressure sensor unit is amplified AC-coupled with a differential amplifier.
• the gain is adjustable.
• This signal changes with the smallest changes in the voltage drop across the sensor and thus with the smallest changes in the pressurization.
• the signal due to the AC coupling is independent of the actual pressurization.
• Resistance determination or installation of the sensor in a resonant circuit The skilled person many ways are known to capture these signals.
• the voltages generated by these electronic structures are quantified, in particular with a microcontroller, which is part of the system in particular, with the aid of an analog-to-digital converter.
• the quantified signals can vary depending on the computing power of the used
• Microcontroller either be evaluated directly or transmitted to an evaluation.
• the transmission of output data or calculated results to an evaluation unit or display unit by radio, e.g. with the Bluetooth standard.
• Each measuring range of an SRS sensor covers a fixed force range.
• the force ranges overlap.
• a fixed force value should not be selected.
• two force values should be selected to initiate the changeover, in particular if the force ranges overlap in order to generate and / or utilize a hysteresis of the changeover. If the force is increased and the force value for the upshift in the current measuring range is exceeded, the next higher one is reached
• the measuring electronics delivers, as shown above, in particular two signals which correspond to the basic pressure ( 5 ⁇ () or the mathematical time derivative of the pressure ( S D ' ⁇ )).
• the basic signals are in particular first converted by a sensor-type-dependent calibration into the SI units N or N / s.
• a calibration can also take place in another unit, or at least be based on another unit, with such a calibration advantageously being converted to the SI units.
• the signal S D ' should change only for changes in the pressure on small time scales, to ensure this is advantageously first determined a running average over the signal.
• the number of measured values since the beginning of the measurement and ⁇ () is the time interval between the measured values S D '(" ⁇ O and S D'(").)
• the time t is given by ⁇ * ⁇ ).
• this factor attenuates the influence of older measured values and prefers newest values. This will prevent yourself
• 11 ß is the active surface of the sensor.
• the measuring electronics supplies, as shown above, in particular two signals which correspond to the basic pressure ( s e ( t )) or the mathematical time derivative of the pressure (SD 'G)).
• the basic signals are in particular initially dependent on a sensor type
• a calibration can also take place in another unit, or at least be based on another unit, with such a calibration advantageously being converted to the SI units.
• the times or rates of changes of the (electronically detected) signals are different. ) changes only gradually with a change in imprint or with a general change in blood pressure. ⁇ />, on the other hand, changes continuously with the pulsating pressure wave, reflecting the activity of the heart. However, due to the electronics, the signal "forgets" changes in pressure over longer periods of time and thus always fluctuates around a zero value.
• the signal should change only for changes in the pressure on small time scales, to ensure this is advantageously first determined a running average over the signal.
• n the number of measured values since the start of the measurement and At (") is the time interval between the measured values S D '(n-1) and ⁇ £>.
• the best positioned pressure sensor unit (s) are characterized by their position directly above the artery. Therefore, at this point, the amplitude of the pulsating pressure wave is maximum.
• This pressure sensor unit (s) is / are advantageously used for the further measurement and / or performance of the method according to the invention.
• the detection of the best-positioned pressure sensor unit (s) is repeated at time-periodic intervals.
• an acceleration sensor is advantageous. With this sensor, the physical movement of the person or animal to be examined can be detected. If the movement is greater than a predetermined limit, re-detection may be triggered.
• the heart pulse is determined from the measured values of the pulsating pressure wave. For this, the measured value curve is examined for prominent points. These may be the maxima or minima in the measuring wave or the measured values or the pressure profile.
• the time interval of two consecutive maxima or minima is the RR interval of the heart pulse in the unit number / minute is given by the following formula: 60s / RR interval in seconds.
• the measured value wave or the course of the pressure is constantly examined for minima and maxima.
• the skilled person are various mathematical models
• a pulse wave velocity results from the measurement of the pulsating
• Pressure sensor units will be distributed on the body or it will be next to the
• Arrangement of the invention also uses other devices for cardiac pulse determination.
• the prerequisite for the use of external devices is an open interface for the collected data and a real-time determination of the data as a heart rate-dependent measured value curve.
• ECG electrocardiogram
• plethysmography based devices can be used which have such open interfaces.
• the measured value curves of the individual devices or of the individual sensors are examined for significant points. In the case of the arrangement according to the invention, these can be the maximas of the measured values of the pulsating pressure wave.
• the distinctive positions of the various devices or sensors have a temporal offset to each other depending on the position on the body. This time offset divided by the distance of the measuring positions to each other gives the pulse wave velocity.
• a sensor array in particular comprising a plurality of sensors described above, has the advantage of easy handling and simultaneous determination of blood pressure and pulse wave velocity.
• FIG. 6 K a possible arrangement of a sensor array is shown in FIG. 6 K. Below is the course of an artery displayed (Fig. 6 Letter L). If two sensors are selected above the artery (Fig. 6 42
• the pulse wave velocity can be determined from the measured value curves of the two sensors (Fig. 6 letter W).
• the respiratory rate can be measured and determined using different methods.
• motion and acceleration sensors can measure the lifting and lowering of the upper body and determine the respiratory rate.
• Sinus arrhythmia is a clear sign of the determination of the respiratory rate.
• the change in cardiac output is directly related to the pulmonary circulation / small circulation. All the blood needs to go through the lungs to absorb oxygen.
• the actual performance can be determined.
• the energy converted per unit of time ie the mechanical power
• continuous motion monitoring can help in the medical application. If, during e.g. the night a reduced cardiac output with increased
• FIG. 1 shows an exemplary illustration of the measuring method.
• the pulsating pressure wave (D) shown as a light gray curve, deforms the artery (L), which at rest shows a constant thickness, between the two horizontal lines in most areas, evenly to the beat of the heart, recognizable by the two consecutive lines Pressure maxima (G), for example, the beginning and end of a RR interval characterized by the artery (L) from its rest position, represented by the horizontal line (F) deformed out.
• the pressure wave fluctuates between the values of the diastolic (minimum of the curve in which the artery has its resting position (B)) and the values of the systolic (A) blood pressure, maxima of the gray curve. This has the consequence that the pressure or the pulse pressure (N) via the arterial surface (E) in the tissue (C), both below and above the artery, is introduced and continues to the skin surface (O).
• the blood pressure is measured by an inventive arrangement (H) with the
• Pressure sensor units (K) is first pressed onto the skin (O) using a rising pressure (J).
• the arrangement according to the invention can be attached to a bracelet (I).
• FIG. 2 shows an exemplary representation of a conventional bracelet.
• a bracelet has a perforated tape (I), wherein protruding perforated tape is locked by a tab (P).
• the arrangement according to the invention can be carried out in the form of this tab and be used instead of this in the bracelet. This has the advantage that on the one hand, the bracelet is already located at a suitable location for blood pressure measurement and 43
• pressure can be exerted on the pressure sensor unit by adjusting the perforated belt.
• Figure 3 shows an example of a cross section through a possible embodiment of the inventive arrangement for use on the bracelet as an essay.
• Arrangement is divided into two parts. The arranged as an array on a convex structure pressure sensor units (K), below the bracelet, and a computational / radio and
• FIG. 4 shows an exemplary electrical circuit of a plurality of pressure sensor units (shown here as 7 ⁇ 15 sensors) in the crossover circuit.
• 15 sensors shown here as 7 ⁇ 15 sensors
• FIG. 5 shows exemplary raw data of an arrangement according to the invention.
• Pressure sensor units provides two measuring signals.
• An unstrengthened signal (R) reflecting the pressure on the pressure sensor unit and an amplified signal (S) representing the
• FIG. 6 shows a schematic and exemplary representation of the measurement of the
• Pulse wave velocity with the help of a sensor array (K).
• the two pressure sensor units (V) lie optimally over an artery (L). Both pressure sensor units (V) are used simultaneously for the measurement.
• the measuring signals (W) are recorded. By examining the measurement signals for significant points, the propagation delay of the two measurement signals can be determined.
• the pulse wave velocity results from the transit time difference divided by the distance between the two pressure sensor units (V) to each other.
• FIG. 7 shows examples of possible embodiments of the inventive arrangement of the conductor track arrangements. There are always two tracks together for
• Conductivity measurements used depending on which conductor pairs are used, different measuring ranges can be used.
• a) conductor track arrangements are shown in a round arrangement with as many as desired conductor track arrangements, depending on the size.
• the first embodiment of a conductor arrangement in the column b has four interconnects
• the second and third embodiments interconnect arrangement from above in the column b) each show an arrangement with three interconnect arrangements
• the third embodiment of a conductor arrangement from above in column b) has, due to the different distances between the interconnects, two measuring ranges defined by the corresponding interconnects with clearly different measuring ranges.
• the dimension can also be adapted to the measuring task (see the fourth embodiment of a
• the hexagonal shape of the interconnect arrangement is particularly suitable to cover a larger area gap-free as possible.
• FIG. 8 illustrates a printed conductor arrangement with three printed conductors, a first measuring region being selected, for example, by measuring between "electrode 1" and “electrode 2 (mode 1)" and selecting a second measuring region, 44
• FIG. 9 shows a section through two pressure sensor units arranged next to one another and designed as a VRS sensor.
• Two printed conductors (light) for measuring the conductance or pressure which are arranged on a functional polymer, can be recognized per pressure sensor unit.
• a conductive pattern (dark) and below the functional polymer a conductive layer is arranged to influence by applying a voltage (Up) between them, the measuring range by changing the properties of the functional polymer.
• FIG. 10 shows a section through two pressure sensor units arranged next to one another. Each pressure sensor unit has above the functional polymer (also
• each pressure sensor unit has two interconnects with a small gap between them (each interconnect arrangement can be seen twice on average due to the meandering arrangement.) Furthermore, each pressure sensor unit has two interconnects below the functional polymer (also pressure-sensitive polymer) with a greater distance between them The individual pressure sensor units are separated by a non-conductive polymer.
• FIG 11 is an exemplary construction of a measuring system for measuring
• the electrical signal for measuring the conductance is first processed by electronic filters. It is then digitized and sent to an evaluation and display device.
• the indicator e.g. a smartphone handles the evaluation and display of the measured data.
• FIG. 12 shows a schematic diagram of a possible embodiment of the invention
• FIG. 13 shows a schematic diagram of a possible embodiment of the invention
• inventive device used as part of a voltage divider (a).
• the measuring range is set by applying a voltage (U P ) across the polymer.
• U P voltage
• b) is shown a typical measurement of the conductance values as the voltage (U P ) changes, which measures such a device during a pressurized process.
• FIG. 14 shows a section through a pressure sensor unit according to the invention. It has a carrier 1 and conductor tracks 4 arranged thereon, of which only one can be seen in the view. They are in particular arranged like an arrangement of FIGS. 7 or 8. Furthermore, it has a functional polymer 6 which has a conductive coating 3 made of a conductive polymer. It also includes a design 2 in the form of a ball cap and feet 13 with which it is placed in depressions 5 of the carrier 1. If pressure is exerted from above and / or below, the functional polymer 6 deforms, in particular first the feet 13, and the conductive coating 3 contacts the conductor tracks, first with a relative one 45
• the functional polymer 6 is further deformed.
• the feet 13 continue to deform and flatten off the curvature of the ball cap 2 and the conductive coating 3, so that the contact area between tracks 4 and more conductive
• Coating 3 is increased. This further reduces the contact resistance between the conductor tracks 4 and the conductive coating 3.
• FIG. 15 shows a section through another embodiment of a pressure sensor unit according to the invention. It has two metallic conductors 7, which are each fused into a conductive layer 8 of conductive polymer. Between the conductive layers 8 there is an insulating layer 9 of an insulating polymer or lacquer. This has holes 10. Within these holes 10, the conductive layers 8 approximately complementarily shaped extensions 11 and 12. When pressure is applied from above and / or below, the insulating layer 9 is compressed and the approximately complementary shaped
• Supports 11 and 12 begin to touch at small points, lines or surfaces.
• the resistance between the conductive layer 8 drops and the conductance between you increases.
• the insulating layer 9 is further compressed and the approximately complementarily shaped extensions 11 and 12 continue to deform in the direction of complementary shaping, so that their contact area is increased. This further reduces the contact resistance between the two conductive layers 8.

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• Health & Medical Sciences (AREA)
• Life Sciences & Earth Sciences (AREA)
• Cardiology (AREA)
• Surgery (AREA)
• Heart & Thoracic Surgery (AREA)
• Veterinary Medicine (AREA)
• Physics & Mathematics (AREA)
• Public Health (AREA)
• Biophysics (AREA)
• Pathology (AREA)
• Engineering & Computer Science (AREA)
• Biomedical Technology (AREA)
• General Health & Medical Sciences (AREA)
• Medical Informatics (AREA)
• Molecular Biology (AREA)
• Animal Behavior & Ethology (AREA)
• Physiology (AREA)
• Vascular Medicine (AREA)
• Hematology (AREA)
• Dentistry (AREA)
• Ophthalmology & Optometry (AREA)
• Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)

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• 2018
  • 2018-03-13 WO PCT/EP2018/056275 patent/WO2018167082A1/de unknown
  • 2018-03-13 US US16/493,913 patent/US20200121201A1/en not_active Abandoned
  • 2018-03-13 JP JP2019571776A patent/JP2020510512A/ja active Pending
  • 2018-03-13 CN CN201880031831.1A patent/CN111491556A/zh active Pending
  • 2018-03-13 EP EP18721690.8A patent/EP3595521A1/de active Pending
• 2019
  • 2019-09-15 IL IL26936219A patent/IL269362A/en unknown

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