EP3595521A1

EP3595521A1 - Method and device for the time-resolved measurement of characteristic variables of the cardiac function

Info

Publication number: EP3595521A1
Application number: EP18721690.8A
Authority: EP
Inventors: Holger Redtel
Original assignee: Micro Giant Data Technology Shenzhen Co Ltd
Current assignee: Micro Giant Data Technology Shenzhen Co Ltd
Priority date: 2017-03-13
Filing date: 2018-03-13
Publication date: 2020-01-22
Also published as: IL269362A; JP2020510512A; WO2018167082A1; US20200121201A1; CN111491556A

Abstract

The invention relates to the time-resolved measurement of the blood pressure, the arterial elasticity, the pulse wave, the pulse wave transit time and the pulse wave velocity and/or changes of the cardiac output and/or of the cardiac output of an object, namely a human or animal body, using pressure sensors for time-resolved measurement of the energy pulse wave. According to the invention, a pressure sensor unit is provided for the time-resolved pressure measurement of the pressure exerted onto the skin by a pulse wave, wherein the pressure sensor unit is an air and/or gas pressure sensor and/or is designed to change at least one electrical conductance and/or resistance when subjected to pressure. In particular, the pressure sensor unit has at least two conductor path assemblies, in particular networks of conductor paths, and a functional polymer which is designed to be compressed when subjected to pressure and to produce and/or change the contact between the conductor path assemblies. Alternatively, the pressure sensor unit has at least two conductive layers with an intermediate space arranged between them, and the pressure sensor unit may be configured in such a manner that, by being subjected to pressure, the intermediate space is compressed and/or in particular the capacitance of the arrangement consisting of the two conductive layers changes.

Description

METHOD AND DEVICE FOR TEMPORARY MEASUREMENT OF

KEY SIZES OF HEART FUNCTION

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

Changes in the cardiac output and / or the cardiac output of an object, namely a human or animal body, using pressure sensors for time-resolved measurement of the energetic pulse wave. 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. Thus, for example, 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.

This temporal accuracy coupled with the possibility of measuring at different points of the body allows the determination of the individual characteristics of the body

cardiovascular system.

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

at least one pressure sensor unit for time-resolved pressure measurement of the pressure exerted on the skin by a pulse pressure, wherein 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. In particular, 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.

If one speaks of a conductance or resistance, in particular an electrical conductance or electrical resistance is meant.

Alternatively and / or additionally, 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. Will one

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

used. In general, 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.

In general, 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.

In particular, the system has an actuator which is set up to press the sensor unit against the skin.

In this case, it has in particular a device for measuring the conductance of the at least one pressure sensor unit. In particular, 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. In particular, 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. Alternatively or additionally, 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. By compressing the non-conductive polymer, also a functional polymer, by pressure, a contact between the arrangement is made of at least one conductor in each case and the contact is intensified with increasing pressure, so that there is a dependent on the pressure of the compression conductance.

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.

The object is also achieved by 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 according to the invention 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

Use of one or a plurality of pressure sensor unit (s) according to the invention 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

1 0kg / cm ^A 2. In particular, 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

be executed for example as a glove. In particular, the artificial skin comprises a sensor array of a plurality of pressure sensor units. In particular, in a sensor array in this case and in general the printed conductors and / or at least one conductive layer of a plurality of pressure sensor units, in particular all pressure sensor units, arranged on a common one-piece carrier and / or the functional polymers and / or designs of a plurality of pressure sensor units, in particular All pressure sensor units, jointly formed in one piece and glued to the particular carrier. The object is also achieved by a method for, in particular time-resolved, pressure measurement, in particular the blood pressure, the

Arterial elasticity of the pulse wave transit time, the pulse wave velocity, the pulse wave and / or changes in the cardiac output and / or and or the cardiac output, by changing an electrical property, in particular a capacity Resistance and / or a conductance between at least two

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. In this case, 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.

In this case, 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.

In this case, the pressure can be transmitted by pressing a pressure sensor unit, in particular designed as described in this document, and / or

in particular by pressing an enclosed and pressurized gas, in particular air, volume on the functional polymer and / or such

Pressure sensor unit to be transmitted. In this case, the pressurization can be used in particular for pressing. In particular, the pressurized gas has a pressure between 50 and 300 mmHg and / or between 6kPascal and 40kPascal.

In particular, 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.

Under an air bag 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.

In particular, when using a pressure sensor unit which is not intended to be pressed against the skin, and / or on the airbag, in the airbag and / or in a fluidically connected to the airbag volume and / or adjacent to such a volume or the airbag is arranged or is, in particular a means for calibration provided and / or in particular a calibration is made to the

Influencing, for example damping, by the coupling and / or the airbag to compensate. For this purpose, 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. In this case, 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. At a certain pressure in the air pressure cuff, 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. However, 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. For this purpose, in particular 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. Alternatively, for example, 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.

In particular, it is determined from the guidelines and / or the change in and / or one and / or the pressure and / or a change in the pressure. In particular, 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.

In particular, 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

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 of the pressure of the pulse wave in the systole, in particular at the place of measurement and / or to a value so low that the measurement signal, in particular conductance, resistance or capacitance, the at least one pressure sensor unit still has a variation with the heart pulse, which is usually up to 80% of the pressure of the diastolic blood pressure possible.

In particular, 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

Influenced with the first systolic blood pressure, the back pressure and / or contact pressure under the 1, 1 times the first systolic blood pressure or below the first systolic blood pressure or on the mean between diastolic or systolic blood pressure or removed and the ratios of the then measured conductance to the first guide values and / or the ratios of the pressures to the first systolic blood pressure associated with the then measured guide values are used as a factor to determine from the first systolic blood pressure, the current blood pressure, the current arterial elasticity, the current one

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.

In particular, 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.

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.

In general, instead of one or more conductance values, it is also possible to use one or more resistors. Maxima and minima must be exchanged accordingly, since the conductance represents the reciprocal of the resistance.

In particular, a polymer which conducts resistance and / or conducts can be produced in two ways. First, 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

Material class compared to normal polymers. Therefore, costs are high and the variability of the properties in today's variants is not sufficient for sensor construction.

For example, 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. As resistive and / or conductive polymer, 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

Life expectancy of a sensor is low. A 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.

Since 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.

Improvement studies showed that even hydrogen peroxide produced a positive impact. This is particularly advantageous since it is a cheap, relatively harmless and relatively environmentally neutral chemical compared to other peroxides. But they are longer

Exposure times necessary.

Higher reactivity of hydrogen peroxide can be achieved in two ways. On the one hand, during the exposure time, the temperature can be increased. On the other hand, the polymer can swell by a solvent, whereby an increased diffusion into the material is possible. Typically, 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

to detect human pulse wave, in particular with an inaccuracy of at most 10% with respect to pressure and / or time of pressure maxima and / or pressure minima, with respect to the time, in particular within a pulse wave and / or an accuracy of 10ms or better. In particular, 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.

Since an accuracy or a data acquisition rate of the pulsating pressure wave, in particular of one millisecond, is achieved, 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

Handling the values for the value of the diastolic or systolic portion of the conventional blood pressure value. In addition, from the time interval of the minima or the maxima to each other, the current heart pulse can be determined and that from pulse to pulse, which allows the calculation of the pulse wave variability. In particular, 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. Thus, measurements of the pulse wave transit time are

Measurements at different measuring points possible.

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.

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.

Also, the elasticity of the arteries can be calculated from the pulse wave velocity e.g. be determined with the Moens-Korteweg formula.

In addition, the temporal resolution of data acquisition, including data acquisition rate, 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.

As will be described below, according to the invention for a measurement

especially as follows. 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

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. Will the

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

Recognize increase in maxima. 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

Pressure value of a minimum of the measured value wave and / or the pressure associated with a minimum the diastolic blood pressure.

In each case a maximum corresponds to a systolic blood pressure of a pulse wave and a minimum to a diastolic blood pressure of a pulse wave.

Especially if at this counterpressure or contact pressure, from the next

Increase no further increase in the maxima of the measured value wave and / or the measured values can be seen, a continuous measurement can be carried out, in which each pressure value of a maximum of the pressure and / or the maximum of the guide values

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.

With particular advantage, 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 the same time, in particular 5 to 20 pressure values and / or pressure values for 5 to 20 pulse waves are displayed.

With particular advantage, 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.

Particularly advantageously, 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.

In this case, in particular at two except for the left / right arrangement of the same limbs, in particular on the same blood vessels, in particular arteries, measured, in particular at identical locations opposite body sides.

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.

There are none in the pressure sensor units described in this patent

Influenced by acceleration forces.

The reason for the optional use of 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). By knowing the current altitude for the HIP, 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.

When using a sensor array comprising a plurality of, in particular adjacent, pressure sensor units, the sensor can be selected, which is most optimal over an artery, this increases the ease of use, since a complex placement of the sensor module is not necessary. Furthermore, 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,

especially with the aid of the evaluation unit, calculate a pulse transit time.

In another inventive arrangement according to this patent, 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.

Using pressure sensor units that measure by force, the sensor can be placed directly on the skin, see Fig. 1 letter O. Favor is 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

Sensor size less painful. This is especially advantageous in a continuous long-term measurement.

The pressure sensor units and an evaluation unit can be used alone.

Advantageously, however, 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.

If the 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. Advantageously, the inventive arrangement and / or the system can also be extended by an actuator which a base pressure or contact pressure on the

Can exert pressure sensor unit and / or presses the pressure sensor unit and / or the sensor array with a base pressure or contact pressure on the skin and / or presses. However, the inventive arrangement can also be operated without an actuator.

As will be further described in this specification, the inventive arrangement can be mounted on the body so that pressure can be applied to the body by the pressure sensor unit.

In particular, 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.

Theoretically, a type of technology, such as an 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.

In most cases, however, 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. However, 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

consistent pressure measurement developed. Strong fluctuations in the continuous recording of measured values lead to unfitness in the measurement of weight and thus also the medical application.

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.

However, calibration with the aid of one, in particular in the system, is advantageous

included, vibration motor and / or by varying the contact pressure by the

Vibration motor performed. This can be done by suitable electrical circuit, the

This is known to the expert, apply a defined pressure to the sensor and thus perform a calibration. For example, a pressure sensor unit may be attached to the inside of a belt. Between sensor and belt, the vibration motor can be arranged.

If the motor vibrates, this band and sensor will push apart, or if the band is worn on the arm, this separation will lead to a change in the contact pressure of the belt Pressure sensor unit on the skin. In particular, thus, a vibration motor between

Enclosing device and pressure sensor unit arranged.

Advantageously, however, a factory, especially unique, calibration is used.

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.

Advantageously, the following requirements should be fulfilled for the sensor:

• Flexible shape, so that the sensor can adapt to the respective measuring point on the body and / or

• Soft design of the sensor to prevent injury and / or

• A shape that adapts to the body to maximize coverage of the sensor and / or

• A small sensor size, advantageously with a diameter of 5mm or smaller. However, larger and smaller sizes are possible and / or

• Have a consistent quality of the measurement, if possible without calibration. A continuous measurement over two weeks or more must at least be guaranteed 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

• Have a print resolution of 0.5mmHg or smaller and / or

• Have a time resolution of 1 ms or less and / or

• The sensor should attenuate the signal as little as possible and / or

• Weather and moisture proof. This also includes the resistance to perspiration and / or The measured value determination must be possible with low energy consumption in order to achieve a mobile measurement, e.g. To enable battery power and / or

• The measured value determination must be possible with a few other components in addition to the actual sensor to allow a small design.

Therefore, 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.

Advantageously, an SRS sensor (switchable resistive sensor) can be used to measure cardiac output. 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. With particular advantage, the measuring areas overlap at least partially and / or they have different sizes and / or spans. In particular, 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. Furthermore, the individual measuring ranges are independent of each other, i. the measurement of blood pressure is simultaneous in the different

Measuring ranges and thus in particular in different accuracies and / or in different measuring ranges and / or admission areas possible. Advantageously, the admission areas overlap. In comparison to other sensor types, for example FSR sensors (Force Sensing Resistor) from Interlink or piezoelectric sensors, 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. In addition to the movement of the body, for example, temperature changes or

Drugs lead to a sudden change in the blood pressure signal.

Unlike FSR sensors, SRS sensors have at least three

Track assemblies or trace networks on or conductive layers, whereas FSR sensors have only two trace arrangements or networks. VSR sensors also have only two, in particular, for the reading of the conductance values and / or resistances

Track assemblies or trace networks on. At least one more

Trace arrangements or trace network or electrode, however, is necessary for the induction.

A printed conductor arrangement, a printed conductor network, or an arrangement of a

Track network has at least one conductor section, in particular a plurality

Conductor sections on, in particular branched and or flat and / or finger-like and / or tortuous, it / they may have meshes and / or openings and / or

be formed labyrinthine.

The 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.

However, since polymers, especially for use in 3D printing, are fusible, another variant of the compound results by heating the metallic conductor and pressing it into the polymer conductor. As a result, the polymer conductor melts locally and the metallic conductor sinks. After cooling, there is an electrical contact. Thus, the metallic conductor may be embedded in the polymer.

To improve the mechanical and electrical connection, the end of the metallic conductor may be formed in the form of a net or one or more eyelets

Because 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.

Another advantageous sensor is the VRS (Variable Resitive Sensor). This is a sensor whose measuring range can be changed by electrical induction. In this case, the measuring range is changed in particular by induction into the functional polymer of the sensor or of the pressure sensor unit. Thus, even with this type of sensor, a large measuring range can be covered.

In the case of the VRS sensors, 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. The

Range selection is arbitrary by the degree of electrical induction.

In general, the conductor track arrangements, conductor track networks and / or at least one conductive layer are arranged in particular on an electrically insulating carrier layer.

When using this sensor type, there are basically two measuring methods. On the one hand, a fixed measuring range can be set, which is only changed if necessary, the signal of the pulsating pressure wave is measured directly. On the other hand, 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.

However, in particular only two interconnect networks are used, between which the resistance is measured and used as a measured value. In particular, 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. Between the further (fourth) conductive layer and the third interconnect network, the electrode and / or third conductive layer, a voltage is applied, in particular to Induce a voltage and / or the

Properties of the functional polymer to change.

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.

Without applied stress, these particles are randomly oriented. By applying a voltage, the particles orient themselves along their dipole moment. The average angle of the orientation of the particles to the field of applied voltage depends on the magnitude of the applied voltage. The electrical properties perpendicular to the voltage field, ie in the measuring direction of the resistance of the sensor depend on the distance of the conductive particles in the measuring direction. If rod-shaped particles are used which are aligned perpendicular to the sensor surface at an applied voltage, the distance of the particles in the measuring direction (parallel to the sensor surface) increases when aligned and the internal resistance of the polymer increases. For the same resistance between the first two interconnect networks, the polymer must now be pressed more tightly against the interconnects, resulting in a smaller contact resistance that outweighs the now greater internal resistance of the polymer. The measuring range of

Loading is postponed.

Functional polymers that can change their mechanical properties by applying an electrical voltage are summarized under the collective term electroactive polymers. For example. The polymer Nafion can be used. This deforms when a voltage of 1 to 5V is applied.

On the electroactive polymer may be applied from both sides of an electrical surface and deformable contact. On one of these electrical contacts will

In particular, a layer of electrically conductive polymer applied, advantageously, a non-conductive layer is applied between the electrical contact and conductive polymer.

An applied voltage across the electrical contacts leads to a deformation of the 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.

When a voltage is applied, 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

resistance-conductive and / or conductive surface portion 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. In particular, the printed conductors should not be completely exposed, but should be so exposed that the functional polymer can contact them by touching them electrically.

Therefore, in practice, both the arrangement of the tracks and the properties of the polymer are adjusted for the application.

With the SRS sensor, in particular, 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.

For a quick and inexpensive adjustment of these parameters, it has proven to be advantageous to insert a further non-conductive polymer layer.

The procedure of setting the tracks is thus carried out by first a sensor is made, which corresponds to experience about the requirements. Now, between the interconnects and the resistance conductive polymer another

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.

If an optimal area ratio is found, 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

Pressure sensor unit. The resolution results from the interaction with the mechanical

Properties of the polymer. If an identical polymer is used: the smaller the distance, the higher the resolution. However, this is countered by the maximum measuring range. There must be a trade-off between resolution and maximum measuring range.

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

Pressure load does not change the conductance.

At higher loads, there is already an electrical contact between the tracks and the contact is improved when the polymer is in contact with a larger area on the tracks. If, as the load increases, the contact area increases over an area which is either only covered by one or no trace network, then there is no change in the measured value and this load area is not recognizable. The accuracy results from the size of these blind load areas. One possible arrangement, which has been found to be suitable in many applications, is given by alternating equal width or thick strip conductors, with a spacing between the strip conductors corresponding to half the width or thickness.

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.

For the optimization of the PCB layout, there are generally different principal

Approaches. For example, the tracks can be varied in width and arrangement, so that there is a different area coverage with tracks.

For example, 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 more the traces are covered, the more apply is required to produce good electrical contact. The maximum measuring range increases. As an example, consider 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.

If concentric rings were then applied as a coating, loading areas would increase as the load increases, and the contact area only increases over the painted areas, ie. In these load ranges, the measured value remains constant and the sensor can not detect this measuring range. This phenomenon is to be avoided, so with a hemispherical or spherical cap-shaped polymer, star-shaped markings are better.

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 50μιη other heights can also be produced, however, a height of Ομιη is not displayed. If the sensor is loaded, the printed conductors are just pushing into the polymer. This leads to an increased

Stress at these points in the polymer and it can lead to abrasion, the quality of measurement decreases. To prevent this, an ideally smooth surface would be desirable.

In order to achieve this at least approximately, 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. However, since 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.

Therefore, an improvement can be made by two paint finishes or are available. First, or is a paint applied in the spaces, which is designed slightly narrower and / or smaller than the negative of the conductor tracks and / or tracks and / or as the

Interspace between the tracks, so that a shift in the paint does not cause that is painted on the tracks and / or is. This first coating is relatively thick, in particular by 10 to 30% and / or 3 to ΙΟμηι lower than the conductor tracks, for example, in conductor tracks with the height of 35μιη the coating is for example 30μιη thick.

Subsequently and / or above, and / or a second coating is applied, which is thinner than the first, in particular 2 to 20μιη 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.

In addition to the conductor track arrangements, 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. In particular, 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.

The adjustment or optimization of the functional polymer requires precise knowledge of the circumstances of the measurement.

In the case of measurement of blood pressure, pulse wave and / or changes in the blood pressure

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. In addition, a high data acquisition rate of at least 1000 values per second should be possible.

Advantageously, 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.

This is possible in particular in two ways. On the one hand, 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.

You can also set both properties separately. For this purpose, a design with a material having a higher Shore hardness compared to at least one other used in the design material is produced. This design is

in particular larger than the surface of the strip conductors, sections, arrangements and / or interconnect networks, in particular the surface of the interconnects assigned to the design, sections, arrangements and / or interconnect networks of an array. Such a construction has, in particular at a location which comes into contact with the printed conductors during use, a surface which is formed by a silicone with another Shore hardness, which is lower in comparison, and in particular is resistant and / or conductive. In addition to silicone are in particular all polymers, which are commonly referred to as rubber, if they meet the mechanical properties mentioned below.

In addition, 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.

Another possibility of 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

Force to nestle against the tracks and depending on the force to increase the contact area. Roughly a hemispherical shape or spherical cap has proved to be the starting form. The flattening to the outside and the design of the central location are adjustment parameters.

In particular, 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.

For the conductance between the conductive layers and / or printed conductors, 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

Setting the and / or the contact to the tracks so the contact resistance. This depends in particular on the surface design of the functional polymer, in particular its microstructure.

The task of the functional polymer is, in particular, the conductive polymer of the

To push printed conductors away and thus build up a counterforce, this is accomplished in particular with spacers or feet (see below). If the sensor is loaded is the

Total force on the conductive polymer and thus the ability to make contact between the

Conducting tracks given as force on the sensor minus drag of the feet. Thus, the more counterforce the feet can provide, the higher the range of measurement to be achieved. As a rule, 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. For the measurement of the pulsating pressure wave in the arteries has a material for 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 3 mm, in particular between 1 and 2 mm and / or a total area of the spacers, in particular in cross section parallel to the planar extension of the conductor tracks and / or conductive layers, between 3 and 5 mm ^A 2 and / or a number of 3 to 4 feet and / or 1 bi s 2 proven as rings running feet.

For the spacers, for the functional polymer, for the design and / or the ball cap, the use of silicone has proven particularly useful. In particular, 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.

In particular, 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. In particular, the

Ball cap and or the segment of a coating of conductive polymer. In particular, functional polymer of the design and / or spherical cap are made of silicone. In particular, feet are arranged laterally next to the ball cap and / or the segment.

In particular, 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.

This results in the meanings or tasks of the individual polymers. 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

Resetting ability has. That is, the strain and the relief movement should be in their Speed of the pulsating pressure wave can follow. On the other hand, the functional polymer, in particular resistance-conductive and / or conductive polymer, in particular a resistance-conductive and / or conductive coating, is characterized in that, depending on the mechanical load, it conforms more or less to the conductor tracks. In this case, 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.

If the polymer comes in contact with a conductor track are initially only a few

microstructural elevations in contact with the conductor track and a high electrical

Resistance between polymer and conductor is present. As the pressure on the polymer increases, the microstructure deforms and the true contact area increases by flattening microstructural protrusions, electrical contact improves, and there is little electrical resistance between the conductor and the polymer. When unloaded, the flattened microstructural elevations relieve themselves and the initial shape is formed back.

In this case, 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. In the center of the functional polymer, in particular the resistance-conductive and / or conductive polymer, in particular the resistance-conductive and / or conductive

Coating, a projecting beyond the shape of the functional polymer, in particular the resistance-conductive and / or conductive polymer, in particular the resistance-conductive and / or conductive coating, protruding survey can be inserted. These

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.

In addition, 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.

It has been found that holes or depressions in the circuit board or a carrier on which the conductor tracks are arranged, in which the spacers and the feet partially or at the points of the feet, the feet or spacers can stabilize very well, so that no lateral movements can occur.

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.

In addition, 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

Burden.

An optimization he can follow by an annular and / or concentric foot shape is selected. 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.

Both parameters can influence each other. The higher the ring, the thicker it becomes because of the deformation when the sensor is loaded. A high ring also leads to an increase in power consumption.

In particular, 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.

The structure of polymer pressure sensors described so far is based on the fact that a conductive polymer is pressed onto two separate networks of metallic conductors. Depending on

Contact pressure changes the electrical contact between the metal tracks and the polymer. The polymer produces a resistive contact between the two tracks. In this case, 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

Material, in particular polymer. These surfaces or layers are arranged one above the other and separated by a further layer or surface of a non-conductive polymer or non-conductive paint. The two surfaces or layers of the conductive polymer are electrically contacted and in particular the resistance and / or conductance between the two surfaces is measured.

Advantageously, 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. For example. Is an arrangement possible, in which with layered Polymer layers in the form of a fingertip vital data are recorded at the A. radialis. The sensitive surface is advantageously on the surface of this finger berry shape and therefore curved.

In particular, the design of the non-conductive surface or layer is crucial for the possible measurable measuring range.

In the simplest case, 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. When the sensor is energized, 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. Depending on the application, 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

Conductivity between the surfaces of the electrically conductive polymers.

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. For this purpose, 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. Advantageously, 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

for example, half a hollow ball in half a solid ball. Further, intermeshing spherical caps and negative shapes with different or equal radii may also be used for the two conductive surfaces.

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.

In such a design of the pressure sensor unit with non-conductive layer between two conductive layers, 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

Layers, in particular their extensions in the resting state, a distance between 0.05 and 0.5 mm, in particular between 0.05 and 0.2 mm. In particular, 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. In particular, 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. For 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. A

Application change in a small (basic) loading leads to a different deformation than the same application change in a higher (basic) exposure due to the different air pressure in the sensor.

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.

If an opening is created and / or arranged between the cavities and a pump, a pressure can be generated in these cavities with a pump, whereby the deformability of the cavities can be changed. The more pressure there is in the cavities, the more difficult it is to deform the cavities, and this means that more strain is needed on the deformation. The measuring range is adjustable with the pressure in the cavities.

Up to this point, only the design of a sensor with a measuring range or with a dynamically adjustable measuring range has been presented. The use of multiple independent measuring range is also possible. For this purpose, further surfaces of non-conductive and conductive polymer are alternately applied and / or arranged. Each additional surface of conductive material increases the range of measurement by one.

If two measuring ranges are to be used, then three surfaces of conductive polymer, separated from two surfaces of non-conductive polymer, are required. For various measurement ranges, 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.

If an extremely high number of measuring ranges is required, the combination of both strategies can be used to increase the measuring ranges.

If an arrangement is used in which there are two surfaces of strips which are rotated against each other and are arranged one above the other, so that the strips of one surface are perpendicular to the strips of the second surface, the location of the load can be determined. It can also be used more surfaces consisting of strips, which are not necessarily aligned perpendicular to each other. Each strip is electrically contacted individually and the

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.

In addition to the actual sensor development, the 3D printing also offers the possibility of

Integration of a sensor or several sensors in the housing or fastening elements of a wearables. The housing or the fastening elements of the 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

Plethysmography using special light conductive 3D-printable materials or

Air cuffs with pneumatic air pressure sensors for measuring blood pressure according to the Riva Rocci method. Thus, the housing with the fasteners is 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.

In particular, one can see with the naked eye in humans the arterial pulse at the A.

Radialis recognize.

The blood pressure from the heart, thus not only felt in the periphery of the human or animal, but also visible.

This pressure is particularly noticeable on the wrist. Here, the radial artery (see Fig. 1 letter L) runs under the skin, but close enough to the surface not to fully affect the cushioning properties of the tissue (See Fig. 1 letter C). If you look closely, you can usually see a pulsating tissue.

The pulsation is produced by the temporal change in pressure at each individual heartbeat.

In the expulsion time of the individual heart rhythms, the pulse wave (see Fig. 1 letter D) is also generated. This can be registered peripherally as the first reaction of a successful heartbeat.

However, part of the blood volume is not immediately diverted to the periphery. The Windkessel absorbs a portion of the blood volume and releases this portion within a RR interval until complete emptying, measurable as diastole.

This is done to compensate for pressure peaks and the system to the respective

Be able to design load situations adapted.

Arrived in the periphery, the pressure pulse or the current pulse can be registered.

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

External pressure on the artery by opening the airbag.

Now, through the arterial blood pressure, the blood can squeeze through the first opening slits of the passage barrier towards the periphery, and thus within the open artery spread again, there is a knocking sound. The Riva Rocci / Korotkov

Method uses tapping for blood pressure determination.

If a sound of the reopened blood flow is detected, the systole (See Fig. 1 A) is fixed.

If knocking ceases, the pressure in the arterial vessel is balanced and the pressure of diastole (See Fig. 1 (B)) can be measured.

By closely observing the instruments in the Riva Rocci / Korotkow method, the following can be noted: Using an analog pressure gauge to determine the pressure in the air bag, it is possible to observe a pulsation of the gauge needle and thus of the pressure. This can be seen when the air bag is loaded with a pressure that is between diastole and systole. There is an air filling in the airbag, in which the fluctuation is maximum.

The values between which the needle varies would correspond to the values for diastole and systole. However, since the air bag dampens the pressure change and the meter does not have the necessary temporal resolution, the values for diastole and systole can not be determined.

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 (see Fig. 1 E) 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.

On the way to the periphery, the pressure pulse is changed by branching, states of the vessels, as well as the external and internal load.

Thus, 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). However, this record of these electrical signals, although used worldwide, is inadequate to measure cardiac output, because the electrical signal is only the instruction to the heart muscles to perform an action, the actual action of the heart can not be detected.

In the case of illness, it may happen that the electrical signal of the sinus node can not lead to any expectoration of blood.

An example of this is atrial flutter and atrial fibrillation. In these diseases, 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. The heart valves to the

However, heart chambers usually open irregularly with 100-160 orifices per minute. This condition is called absolute arrhythmia.

Thus, there is only an ejection of blood with a frequency of 100-160 per minute.

Of course, such diseases lead to recognizable patterns in the ECG signal, which can be recognized by those skilled in the art. However, it depends on the experience and training and especially on the knowledge of all possible diseases in the professional.

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. Thus, 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.

By virtue of the recording of a measured value curve which maps the pulsating pressure wave, the arrangement according to the invention permits the time intervals between each individual heart pulse to be determined. These intervals are called RR intervals.

For example, 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.

In addition, the pulse wave velocity must not be confused with the speed of the blood in the arteries, this is much slower.

Starting from a heart pulse, 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. These

Deformability is the elasticity of the arteries.

Thus, the elasticity of the arteries can be determined by measuring the pulse wave velocity. To determine this, 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.

In case of illness, the elasticity may e.g. be excessively reduced by arteriosclerosis. Therefore, the elasticity is a characteristic, e.g. warn of impending heart attacks.

In addition, studies have shown that, at least over short periods of time

Pulse wave velocity can also be used to monitor the blood pressure.

For the measurement by the inventive arrangement in particular two approaches.

On the one hand, the pulsating pressure wave can be measured with several sensors at different points of the body. Thus, 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.

Since the inventive arrangement has a high data acquisition rate, the sensors can also be close to each other. This allows the measurement of

Pulse wave velocity local to the body.

On the other hand, 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. For the athlete, therefore, 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.

Another area of application, which arises due to the connection with the oxygen supply, is the patient control during operations. Cardiac output is already measured continuously in many surgeries, but this is done invasively using a variety of methods. 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.

In summary, the methods for cardiac output determination are either very inaccurate or require an intervention in the body that is only justifiable in exceptional situations.

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.

Only the absolute diameter or radius of the aortic arch in diastolic blood pressure can not be determined by an inventive arrangement and must be compatible with external devices e.g. Ultrasound to be determined. However, in a continuous long-term monitoring not so much the absolute value plays a role, but the changes. 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. However, 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.

Thus, the ejection volume of a cardiac pulse, even without further correction by the elasticity can be approximately determined as follows:

The currently 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 ^E :

ß (t) = R ₀ + E * P (t)

Here 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.

To calculate a volume, the length ^L of the artery deformation in a cardiac pulse must be determined. For this, the temporal length of a cardiac pulse, the RR interval ^T , and the pulse wave velocity ^{v are} linked:

L = v * T

SHEET INCLUDED BY REFERENCE (RULE 20.6) 30

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 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.

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 -:

m fairan R. _m me _* mi rn

Here, ^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.

I_E3 v * C3 31

Since the current time t (start time is the beginning of the heart pulse with t = 0) in the pulse with the current position of the pressure wave in the artery l (t) with the Pulswellengeschindigkeit is connectable:

Z (t) = v * t

Can the current radius also be represented as a function of I. R ') = R (// v)

The volume results from the integration of all measured values in a heart pulse under the known formula for determining the cross-sectional area from the radius (area = R ² ):

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

Letter K and O, to be placed.

To obtain a uniformly applied pressure, a wristband, Fig. 1 (I), can be used around the wrist as an aid and as a commercial product. Thus, a uniform pressure, 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. Thus, 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.

The measurement of blood pressure can be greatly influenced by the surrounding tissue. Therefore, precautions should be taken in special cases.

In people with high fat content or moderate expression, it may come at the preferred location for measuring blood pressure and heart pulse on the wrist to increased attenuation of the measurement.

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 the diameter of the lower limb. With a measurement of the variable diameter or the variable pressure on the applied measuring surface with at least one pressure sensor unit, the blood pressure and heart pulse can also be detected here.

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.

For this purpose, preferably for the invention, a specially prepared and clearly defined for the user surface on the bracelet or system can be created. This surface

SHEET INCLUDED BY REFERENCE (RULE 20.6) 31

Since the current time t (start time is the beginning of the heart pulse with t = 0) in the pulse with the current position of the pressure wave in the artery l (t) with the Pulswellengeschindigkeit

can be linked:

Can the current radius also be represented as a function of I. It applies

R '(?) = R (// v)

The volume results from the integration of all measured values in a heart pulse under the known formula for determining the cross-sectional area from the radius (area =? IR):

VE) m 03 {2R. ^* ! HHlPcil {3 TC G9 133 E ^ EHSEP dlG9 TC 13 E33 EG332P vdht

G3 El l2l? J _m E * (2M2ET vd t

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.

Letter K and O, to be placed.

To obtain a uniformly applied pressure, a wristband, Fig. 1 (I), can be used around the wrist as an aid and as a commercial product.

Thus, a uniform pressure, Fig. 1 letter J, can be exerted on the A. radialis.

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

Bracelet and surface of the skin are registered.

The dynamic pressure pulse of the actual ejection of the heart, can by means of

Evaluation and image unit for everyone to be made visible. Thus, the

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.

Therefore, precautions should be taken in special cases.

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

People, for example, by strong water deposits in the legs and especially in the feet.

For this purpose, preferably for the invention, a specially prepared and clearly defined for the user surface on the bracelet or system can be created. This surface 32

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.

For a blood pressure measurement, the user can, for example, a finger on the defined

Lead surface of the bracelet. A gently and steadily increasing pressure increase on the wristband, caused by the build-up pressure of the finger on the marked area, is registered and stored by the system, in particular with the pressure sensor unit, with at least 1000 measurements per second.

The user feels a more perceptible pulsation when gently pressing on the A. radialis. This increase in perceptible pulse does not come from one

Raising blood pressure but by the compression and distribution of the surrounding tissue between the skin surface and the existing tissue above the A. radialis.

Like a squeezed out sponge, the compressed and squeezed tissue forwards the pulsating wave almost 1 to 1 from the arterial wall to the pressure sensor unit. The damping of the fabric, Fig. 1 letter C, is reduced by the back pressure and / or contact pressure of fingers or an actuator, Fig. 1 letter J, from the outside and thus above the skin, Fig. 1 letter O.

To be able to measure the systole of the blood pressure, the back pressure on the artery or pulse wave (see FIG. 1 D) 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.

As the backpressure increases further, the minimums continue to rise, the maxima of the

pulsating pressure wave remain constant.

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.

If only the diastolic blood pressure increases, the distance between the minima and the maxima in the pulsating pressure wave changes. Now the back pressure should be adjusted again 33

will be increased again, in particular starting from a value below the systolic blood pressure, until an increase of the maxima is no longer present.

Only the unlikely event of a falling diastolic blood pressure, with constant systolic blood pressure, can only be recognized by periodically resetting the backpressure, in particular by repeatedly increasing the back pressure and / or contact pressure, in particular starting from a value below the systolic blood pressure until an increase in maxima is no longer possible.

The measurement of the pulse wave transit time and the pulse wave velocity requires the simultaneous measurement of the pulsating pressure wave at different locations. For this purpose, 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 pulsating pressure curve with the at least one pressure sensor unit extends, loaded. The distance of the pressure sensor units, with separate pressure sensor units, must now be measured and transmitted to the inventive arrangement. For a sensor array, these distances are the

inventive arrangement usually known and / or constant. The calculation of the

Pulse wave delay and the pulse wave velocity can now be done automatically.

For a blood pressure measurement, only one pressure sensor unit is necessary, but the use of multiple pressure sensor units is advantageous.

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.

However, 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.

Also, therefore, the blood pressure measurement can be done automatically, for example, during the night and gently. 34

The actuator can, for example, electrically, pneumatically, hydraulically or manually solve by muscle contractions the task of generating the back pressure. Also the

Combining all solutions with each other and against each other allows the application.

An actuator has in particular an airbag and a pump for pressurizing the airbag. In particular, 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.

In particular, 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.

A system, use or method can be extended by two types of other measurement techniques. On the one hand, measuring techniques can be applied at the location of the pressure sensor unit. On the other hand, 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.

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.

For example, 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.

In the Riva Rocci method, 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.

With a combined sensor, 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

However, if a plethysmographic sensor is used, higher accuracy can be achieved. 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.

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. When 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.

To measure the ECG wave, 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

Voltage changes between the two contacts is the ECG wave.

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. With the pressure sensor unit, 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.

On the surface of the support surface of the pressure sensor unit to the skin no additional functionality is housed, so this surface can be coated with an electrically conductive and flexible material. This can represent one of the two electrodes. In particular, a system according to the invention comprises a enclosing device, in particular a band, and at least one

Pressure sensor unit and an actuator arranged therebetween, in particular airbag, and in particular a pump for pressurizing the airbag.

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

This is known to the skilled person.

However, the actuator also has the disadvantage that electrical energy is consumed. This must be calculated in the respective application.

Currently, manual and actuator-controlled locking systems, for example. In

Shoe or in cuffs made by Boa Technology. Also market leaders such as Nike (HyperAdapt 1 .0), Puma (Ignite Disc), Reebok with the "The Pump technology", or the French company Digitsole (Smartshoe 002), have actuators controlled in 2016 36

Locking systems installed in a product for the first time. Thus, "shoe" already has easy automation and integrable requirements for the continuous pulse and

Blood pressure measurement.

But it is also possible to generate the required back pressure and / or contact pressure with the forearm muscles by muscle contractions, eg. By opening and closing the hand. Thus, 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.

A further advantageous invention is the use of a convex structure with a sensor array arranged thereon. 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. In order to be able to measure also non-visible arteries, 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.

To ensure even surface pressure on the artery on the foot or the

To generate forearm / wrist, it is advantageous to incorporate foam or foam-like material between the flexible sensor unit and the Anpresskörper, 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.

In order to be able to correctly place the convex structure, for example in the size of half a pea, 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. 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

Wrist. Without a tab, the protruding perforated tape and without insertion into the tab, (for example, leather bracelet) 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.

Above the 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.

Thus, 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.

Advantageously, while 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.

To optimize a better placement of the invention, for example, the measured value can be transferred to a mobile smart device.

Through a plurality of tiled arranged pressure sensor units, see Fig. 1 letter K, and also Fig. 3 letter K, within and / or on the convex structure, 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.

However, it is also possible with a single pressure sensor unit and also without the use of a convex structure to measure the various characteristics of the cardiovascular system.

The use of a convex structure on the several is advantageous

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. In order to determine the pressure sensor unit, which lies optimally above the artery, 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. In this case, 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. In particular, 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. In particular, m is equal to 2 or greater. Advantageously, 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.

In particular, the best measuring range is determined by the maximum value.

The smaller the measuring range, the more accurate the result.

No matter which variant is used for which application, the data from the

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.

Preferred here is the mobile solution such as a smart device, such as a clock or

Smartphone.

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

Smartphone, or even within the bracelet of fitness trackers.

Thus, furthermore, 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.

This division would not only have sizes and energy advantages, since the smart devices already have a complete infrastructure for operation and evaluation.

The "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). As described further in the patent, for the determination of the central continuous blood pressure, the temporal and spatial resolution to the HIP of

Measuring point in the periphery / extremities advantageous.

In the horizontal storage of the living being, for example, man, the location of the

Neglecting measuring point, since all measurable vessels are located at almost the same height to HIP.

Measurements on the foot usually produce only minor changes in the movement to the HIP.

In order to determine the time course of the blood pressure within a pulse and over several pulses, the height of the HIP should also be determined during physical exercise

(hydrostatic indifferent point) be known. The measured blood pressure e.g. in the arm changes depending on the height above the HIP. The change in blood pressure in the arm due to

Altitude change Ah results as follows:

ΔΡ = a Äh

Here, α is an empirical measurement with the value of about a = 1 mmHg / cm for the systolic blood pressure and about α = 0.5 mmHg / cm for the diastolic blood pressure.

If the current height of the arm is known and the blood pressure Pm in the arm can be measured, the central blood pressure Pz in the HIP can be calculated:

Pz = Pm - ΔΡ

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

Laser pulse), which on a fixed, ie outside the body attached, reference surface 39

is reflected. 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.

From the measured values of the acceleration sensor, for example with the aid of the Velocity-Verlet algorithm, the movement of the arm can be traced and the current location of the arm can be determined.

However, since minute inaccuracies, such as occur in today's acceleration sensors, can lead to large deviations of the location or the height when measuring the acceleration, 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. For this purpose, known motion patterns are compared with the current acceleration data. Will one

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

Use of 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. For this purpose, the voltage which drops across the pressure sensor unit is amplified AC-coupled with a differential amplifier. Advantageously, 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. However, the signal due to the AC coupling is independent of the actual pressurization.

The technical measures described in this example for receiving the measurement signals can also be realized differently. Other examples for receiving the unamplified signal are e.g. the use of a Wheatstone bridge, the constant current method for

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. Advantageously, 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.

Advantageously, the force ranges overlap. When switching, a fixed force value should not be selected. Instead, 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

Switched measuring range. In the higher measuring range, the force value is now

Downshifting less than the force value in the smaller range to upshift. This 40 prevents unnecessary switching back and forth due to measurement noise when the applied force is in the range of the switching limits.

The measuring electronics delivers, as shown above, in particular two signals which correspond to the basic pressure ( ⁵ σ () 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. In this case, 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. ^s c ( ^t ) changes only gradually with a change in imprint or with a general change in blood pressure. ^S D '), on the other hand, changes continuously with the pulsating pressure wave, thus reflecting the activities 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.

Mathematically, the current force results and from this the pressure on the sensor - ^ (at time ^1, for example, by the following approximation:

Here ^l o is a time before the actual measurement, in which applies to all

Times ^t o.

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.

Then the integral of the signal '<() is approximated as a sum:

j S _D '(t) dt * (00 - V00) * At (n)

Here, "the number of measured values since the beginning of the measurement and ^Δί (") is the time interval between the measured values ^S D '("~ O and ^S D'(").) The time ^t is given by ^Δ * <η).

Since errors occur with every numerical integration and since the measured values can also be noisy, the execution of the integral must be further optimized. Therefore the sum is replaced by a recursive sum and the result of the integral Ht) results as:

Here, for the attenuation factor ^{0 <a <1} , this factor attenuates the influence of older measured values and prefers newest values. This will prevent yourself

Sum up calculation error and measured value noise. The factor must be attached to the

used type of sensor to be adjusted empirically.

This results in the measured value of the pulsating pressure wave:

P (t) = β (S _G (t) + I (t))

Here, ¹¹ ß is the active surface of the sensor.

If an array of multiple pressure sensor units is used to use the optimal position over an artery, advantageously all pressure sensor units will initially be used

SHEET INCLUDED BY REFERENCE (RULE 20.6) 40

Prevents unnecessary back and forth due to measurement noise when the applied force is in the range of the switching limits.

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

Calibration transferred to the SI units N or N / s. In this case, 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. ^ύ />, 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.

Mathematically, the current force and hence also the pressure on the sensor F (') at time ¹ results, for example, from the following approximation:

Here, h is a time before the actual measurement in which ^S D '(() ^{= ()} holds for all times ^{t <1;} o.

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.

Subsequently, the integral of the signal ^S D '^) is approximated as a sum:

m Efej 'for J2I2tit El G3 {See,' ΕΕΙΘ IS Efe, '-ZEIHE! * Atelier

Here, ^{n is} 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 ^ύ £>. The time ¹ is given by ^{ΐ =} Σ ^{A t} ^.

Since errors occur with every numerical integration and since the measured values can also be noisy, the execution of the integral must be further optimized. Therefore, the sum is replaced by a recursive sum and the result of the integral Π ') results as:

not a word

Here, for the attenuation factor 0 ^{<a <} l. This factor weakens the influence of older measurements and prefers new values. This will prevent yourself

used type of sensor to be adjusted empirically.

This results in the measured value of the pulsating pressure wave ^p ( ^! ):

m to izizfei m to i for

Here is the active area of the sensor.

If an array of multiple pressure sensor units is used to use the optimal position over an artery, advantageously all pressure sensor units will initially be used 41

read over a period of several heart pulses. This can be carried out simultaneously or sequentially, depending on the capabilities of the measuring electronics. Preferable is a simultaneous reading.

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.

In a continuous measurement, the detection of the best-positioned pressure sensor unit (s) is repeated at time-periodic intervals.

The use of 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.

In particular, the measured value wave or the course of the pressure is constantly examined for minima and maxima. The skilled person are various mathematical

Procedures known.

A pulse wave velocity results from the measurement of the pulsating

Pressure wave at different points of the body. However, the points should be on a line between the heart and the point farthest from the heart.

This can be done by two principal approaches. On the one hand, a plurality of at least two system or arrangements according to the invention and / or

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. For this purpose, for example, electrocardiogram (ECG) or 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.

The use of 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.

To illustrate the use of a sensor array, 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

Letter V), 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. On the one hand, motion and acceleration sensors can measure the lifting and lowering of the upper body and determine the respiratory rate. The respiratory

Sinus arrhythmia (RSA) 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.

In addition, by using acceleration sensors in an inventive arrangement, the actual performance can be determined. By determining the movement of individual body parts, the energy converted per unit of time, ie the mechanical power, can be determined.

The comparison of this theoretical performance from the continuously measured cardiac output and the actual performance allows the prognosis of the expected increase of the lead during athletic training or at

Rehabilitation measures.

Further, continuous motion monitoring can help in the medical application. If, during e.g. the night a reduced cardiac output with increased

Heart rate detected without significant movement can be seen, the invention can draw conclusions about the diseases in question diagnostically. As visual representations for the users come concentric diagrams

advantageously used.

In 2D, 2.5D, or 3D, the sum of the measured data must be displayed clearly. Conventional diagrams with an X and Y axis are confusing and difficult for the user to understand for the number of views to be displayed.

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). In this case, the arrangement according to the invention can be attached to a bracelet (I).

Figure 2 shows an exemplary representation of a conventional bracelet. Such 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

On the other hand, 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. The inventive

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

Energy unit (H) above the bracelet. The bracelet is passed through a slot (I). For measurement, a uniform or increasing pressure (J) is applied from above.

FIG. 4 shows an exemplary electrical circuit of a plurality of pressure sensor units (shown here as 7 × 15 sensors) in the crossover circuit. In this example, 15

Switching cables and 7 test leads needed.

FIG. 5 shows exemplary raw data of an arrangement according to the invention. The

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

Changes in pressure reflects.

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. In this case, a) conductor track arrangements are shown in a round arrangement with as many as desired conductor track arrangements, depending on the size. Under b) is another possible embodiment in the form of a square

Printed conductor arrangement shown in which basically the conductor tracks are arranged helically. In this case, 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. Furthermore, the dimension can also be adapted to the measuring task (see the fourth embodiment of a

Track arrangements from above in column b), which extends into the column c). The upper three interconnect arrangements of column c) show different variants of interconnecting interconnect arrangements. In column d) is another possible

Embodiment of a conductor track arrangements shown that the arrangement of the conductor track can also be made more complex. In this case, 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

by measuring between "Electrode 1" and "Electrode 2 (Modes 2)". By the

Changes in the distance between the tracks used and thus the distance to be bridged by the functional polymer changes the conductance at the same pressure. From a larger distance results in a larger measuring range.

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. In addition, on the functional polymer, 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

pressure-sensitive polymer) 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.

In the figure 11 is an exemplary construction of a measuring system for measuring

Conductances and pressures are shown. 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. In addition, the display device of the

Measuring electronics various tasks, such. the choice of the conductor track, one

Trace area, the repetition rate, etc.

FIG. 12 shows a schematic diagram of a possible embodiment of the invention

Device according to the invention used as part of a voltage divider (a), and a typical measurement of the conductance, which measures such a device during a process under pressure. Due to the larger track distance strives

Measuring range 1 slower against the maximum voltage, as measuring range 2 with the smaller interconnect distance.

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. In 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

high contact resistance and thereby connects the interconnects 4 to each other electrically. As the pressure is further increased, the functional polymer 6 is further deformed. In particular, 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. As the pressure is further increased, 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.

Claims

46 claims

1. System for time-resolved measurement of blood pressure, arterial elasticity, the

Pulse wave transit time, the pulse wave velocity, the pulse wave and / or changes in the cardiac output and / or cardiac output, comprising

at least one pressure sensor unit for time-resolved pressure measurement of the pressure exerted on the skin by a pulse when pressed against the skin, wherein the pressure sensor unit is set up, at least one electrical conductivity and / or resistance

Change the pressure to change

wherein the pressure sensor unit at least two conductive layers and / or

Trace assemblies, in particular trace nets, and a functional polymer that is configured to be compressed by application of pressure and to establish and / or modify contact between the conductive layers and / or trace assemblies;

and / or wherein the pressure sensor unit is an air and / or gas pressure sensor and in particular has at least two conductive layers with a dielectric disposed therebetween and is arranged so that the dielectric is compressed by application of pressure and / or thereby in particular the capacity of the arrangement consisting of the two conductive layers changes,

the system in particular comprising an actuator which is arranged, the

Press the sensor unit against the skin.

2. System according to claim 1, wherein the pressure sensor unit at least one arrangement of, in particular exposed, printed conductors and / or printed conductor networks and a

Resistive conductive and / or conductive polymer, which is pressed onto the at least one arrangement of conductor tracks and / or conductor tracks by applying pressure and / or wherein the pressure sensor unit comprises at least one non-conductive polymer or a coating, which between the two

Arrangement of at least one conductor track and / or between the two conductive layers is arranged and has holes.

3. System according to any one of the preceding claims, wherein the resistance-conductive

and / or conductive polymer has a microstructure which is adapted to deform by the pressure and the contact surface to at least one arrangement of exposed conductor tracks increases and the electrical contact improves and in particular the electrical resistance between interconnects and the

resistance conductive and / or conductive polymer and / or reduced between the interconnects.

4. System according to any one of the preceding claims, wherein the resistance-conductive

and / or conductive polymer is part of the functional polymer, wherein the functional polymer has a conductive surface, in particular formed by the

Resistance-conductive and / or conductive polymer.

5. System according to one of the preceding claims, wherein the actuator is an electrical,

pneumatic, and / or hydraulic actuator is, in particular an electrical

Vibration motor and / or includes an air bag and the actuator is adapted to inflate the air bag with air and / or to apply and in particular includes a pump to press the pressure sensor unit to the body. 47

6. System according to any one of the preceding claims, wherein the system comprises an air bag, in particular in the form of a cuff, and the pressure sensor unit on the air bag, in the air bag and / or in a fluidically connected to the air bag volume and / or adjacent to a such volume or the airbag is arranged, and wherein the system is in particular arranged so that the

Pressure sensor unit can detect the pressure exerted on the skin by the pulse wave pressure applied to the skin transmitted by the gas in the airbag and / or the pressure exerted on the skin by pressing the airbag through the pulse wave pressure is transmitted through the airbag to the pressure sensor unit.

7. System according to any one of the preceding claims, wherein in the idle state of

Pressure sensor unit only a few microstructural elevations are in contact with the at least one arrangement of exposed printed conductors and a high electrical resistance between resistance conductive and / or conductive polymer and conductor is before and deformed by the pressure and / or back pressure, the microstructure and the real contact surface increases.

8. System according to any one of the preceding claims, wherein the pressure sensor unit has a measuring range of at least 40mmHg to at least 300mmHg and / or a

Resolution of at least 0.5mmHg and / or is set to take at least 1,000 values per second and / or has at least a time resolution of 1 ms.

9. System according to any one of the preceding claims, wherein the system further comprises a Kalibrationsaktor, adapted to press the pressure sensor unit with a known back pressure on the skin and / or a back pressure sensor for measuring the back pressure is pressed with the pressure sensor unit to the skin.

A system according to any one of the preceding claims, comprising a calibration sensor, in particular force and / or strain sensor, e.g. Strain gauges and / or a Kalibrationsaktor which exerts pressure by defined contraction and / or vibration motor, in particular a motorized bracelet

11. A system according to any one of the preceding claims, comprising a back pressure sensor for measuring the force with which the pressure sensor unit is pressed onto the skin, for example from a user's finger, in particular at the same time as measurements of the pressure sensor unit, advantageously with at least 1000 measurements per second ,

12. System according to one of the preceding claims comprising a plurality

Pressure sensor units, in particular a sensor array of a plurality of

Pressure sensor units, in particular as part of a sensitive shell, a sensitive surface or artificial skin, in particular a robot.

13. System according to the preceding claim, wherein the plurality of pressure sensor units, in particular a sensor array of a plurality of pressure sensor units, are arranged on a convex surface and / or a convex structure.

14. System according to one of the preceding claims, comprising an evaluation unit for calculating the systolic and / or diastolic blood pressure, the arterial elasticity, the pulse wave transit time, the pulse wave velocity, the pulse wave velocity and / or the relative or absolute cardiac output from the measured values of the 48

at least one pressure sensor unit and in particular the counter-pressure sensor and / or calibration sensor

15. System according to any one of the preceding claims, wherein the pressure sensor unit is not larger than a cherry stone, or 5mm in diameter.

16. System according to any one of the preceding claims comprising at least one

Acceleration sensor and / or sensor for determining the position / height to HIP, in particular an inertial sensor.

17. System according to any one of the preceding claims, comprising a control and / or evaluation, in particular set up, a method according to the invention

perform.

18. System according to one of the preceding claims, arranged, the pressure sensor unit or a first set of pressure sensor units of a plurality of

Determine pressure sensor units, which is placed in the most optimal position and in particular to pass on information to the user, as the user

Placement of the pressure sensor unit can readjust, if the placement does not meet a predetermined requirement.

19. System according to one of the preceding claims set up for connection and / or coupling with at least one external measuring system, in particular ECG device or devices based on plethysmography, for determining the cardiac pulse, in particular for determining the pulse wave velocity, wherein the external measuring systems a Allow real-time measurement of the pulsatile pressure or ECG wave and have an open data interface that allows real-time output of the data.

20. Method for time-resolved measurement of blood pressure, arterial elasticity of

Pulse wave transit time, the pulse wave velocity, the pulse wave and / or changes in the cardiac output and / or the cardiac output, by changing an electrical conductivity and / or resistance and / or a capacitance between at least two conductive layers and / or between at least two conductor track arrangements, in particular printed conductor networks Compressing a functional polymer and / or dielectric by the pressure applied to the skin over an artery by a pulse wave.

21. The method according to any one of the preceding claims, wherein the conductor track assemblies and the functional polymer are pressed with different pressure to the skin and thereby the conductance and / or resistance measured and / or the change in conductance and / or resistance is determined, in particular at least a time resolution of 1 ms, wherein in particular the different pressure is monotonically and / or continuously increased, in particular until the backpressure and / or contact pressure increase, the pulse wave does not increase the measured conductivity and / or and / or decrease the measured resistance and / or or pressure above the maximum measured conductance and / or minimum measured resistance and / or pressure can produce, wherein the pressing is carried out in particular by inflating an airbag.

22. The method according to any one of the preceding claims, wherein from the conductances and / or resistances and / or the change of the pressure and / or a change of the pressure is determined. 49

23. A method according to any one of the preceding claims, wherein the systolic blood pressure is assumed to be the pressure by, with further increasing the backpressure and / or contact pressure, the pulse wave can not produce an increase in the measured pressure beyond the maximum measured pressure and / or the diastolic Blood pressure is assumed as the pressure corresponding to the minimum of the measured values of a pulse wave, when the back pressure and / or contact pressure is selected as the pressure or higher, at which the maximum measured pressure does not increase further with increasing backpressure and / or contact pressure.

24. The method according to any one of the preceding claims, wherein the pressure of the pressing is then reduced to a value, in particular within a range of 1, 5 times, in particular 1.3 times the systolic blood pressure to

complete discharge.

25. The method according to claim 1, wherein the pressure of the pressing subsequently and / or with knowledge of a first systolic blood pressure and / or a first conductance and / or first resistance of the at least one pressure sensor unit is subjected to the first systolic blood pressure of the backpressure and / or. or pressure below 1, 1 times the first systolic blood pressure or below the first systolic blood pressure, in particular to a value below the diastolic blood pressure, as long as the pulsating pressure wave is mapped or removed and the ratios of the then measured conductance and / or Resistance to the first conductance and / or first resistance and / or the ratios of the first systolic blood pressure associated with the then measured conductances and / or resistances are used as a factor for determining from the first systolic blood pressure, the current blood pressure, the current arterial elasticity, di e current

26. Method according to the preceding claim, wherein continuous measurements of the conductance values and / or the pressure of the pulse wave take place with the reduced contact pressure until a change in the pressure maxima of the pulsating pressure wave is detected, in particular by more than 10%, and / or until a change the distance between the pressure minima and the pressure maxima in the pulsating pressure wave, in particular by more than 1 0%, and in particular subsequently the contact pressure is further reduced and then increased again, in particular monotonically and / or continuously increased, and thereby measured the conductance and / / or the change in the conductance is determined, in particular at least with a temporal resolution of 1 ms.

27. The method according to any one of the preceding claims, wherein the pulsating pressure wave is measured with a plurality of sensors at different locations of the body and the pulse wave transit time is determined from the time offset of the measured curves to each other, in particular with knowledge of the distance of the sensors to each other

Pulse wave velocity is calculated.

28. The method according to any one of the preceding claims, wherein the change the

Cardiac output is determined by determining the change in the value of the integral of all measured values, in particular all measured conductance and / or pressure values and / or pulse waves pressure values in a pulse wave, in particular between two 50

systolic and / or two diastolic pressures and / or wherein the cardiac output is determined from the value of the integral of all measured values, in particular all measured conductance and / or pressure values and / or pulse waves pressure values in a pulse wave, in particular between two systolic and / or two diastolic pressures , multiplied by the cross-sectional area of the artery and / or the aortic arch.

29. The method according to any one of the preceding claims, wherein the method is a method for continuous long-term monitoring.

30. The method according to any one of the preceding claims, wherein the counter-pressure and / or contact pressure is applied electrically, pneumatically, hydraulically and / or manually, in particular by muscle contractions.

31. The method according to any one of the preceding claims, wherein the height of the location of

Pressing on the skin for HIP is determined and in particular a correction of the measured values is carried out depending on the height of the site of pressing on the skin to HIP.

32. Method according to one of the preceding claims, wherein an, in particular open, data interface, which enables a real-time output of the data, uses at least one, in particular external, measuring system, in particular an ECG device or a device based on plethysmography, for determining the cardiac pulse is used to determine the pulse wave velocity.

33. Use of the change of a capacitance, a conductance and / or the change of a capacitance, 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 trace networks, by compressing a functional one 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

Cardiac output.

34. Use according to one of the preceding claims, wherein a, in particular open, data interface which enables a real-time output of the data, at least one, in particular external, measuring system, in particular ECG device or a device based on plethysmography, is used to determine the cardiac pulse for the

Determination of pulse wave velocity.