Method and device for noninvasively measuring blood pressure, and housing

Abstract

The present invention relates to a method for noninvasively measuring blood pressure and to a device for noninvasively measuring blood pressure. The present invention also relates to a housing, especially for a device for noninvasively measuring blood pressure.

Description

[0001] Description

[0002] Title of the invention

[0003] Method and device for non-invasive blood pressure measurement and housing

[0004] field of technology

[0005] The present invention relates to a method for non-invasive blood pressure measurement and a device for non-invasive blood pressure measurement. Furthermore, the present invention relates to a housing, in particular for a device for non-invasive blood pressure measurement.

[0006] State of the art

[0007] Methods and devices for non-invasive blood pressure measurement are known from the state of the art. For example, a blood pressure cuff is placed around an extremity of a living being, such as a human upper arm, and inflated with air. The air is then released from the cuff, and the pressure curve in the cuff is measured. Based on these pressure values, the pressure changes in the cuff caused by the living being's pulse waves can be determined and evaluated with regard to blood pressure parameters.

[0008] However, especially in veterinary medicine, the characteristics of pulse waves and typical blood pressure values ​​vary considerably depending on the species. Therefore, it has proven technically and economically challenging to be able to determine pulse waves and, based on them, blood pressure parameters for different animals both reliably and precisely, as well as using simple and cost-effective means.

[0009] Summary of the invention

[0010] It is therefore an object of the present invention to overcome the described disadvantages of the prior art and in particular to provide means by which a non-invasive blood pressure measurement for different types of living beings, and in particular for different value ranges of the living being-typical blood pressure and the pressure changes caused by the pulse waves, is possible both reliably and precisely and with simple and cost-effective means.

[0011] The object is achieved by the invention according to a first aspect in that a method for non-invasive blood pressure measurement, comprising exerting a time-varying pressure on at least part of the body of a living being by means of a compression device at least during a measurement period, in that a first specific fluid pressure within a chamber of the compression device is changed in a time-dependent manner at least during the measurement period by means of a first pressure adjustment device, wherein at different measurement times during the measurement period, at which at least partially different first specific fluid pressures are set, at least one measured value of a differential pressure existing at the respective measurement time between the, in particular current, fluid pressure within the chamber and the, in particular current, fluid pressure within a storage volume is recorded,and wherein a second specific fluid pressure within the supply volume is adjusted by means of a second pressure adjustment device, in particular at least during the measurement period, wherein preferably by means of the second pressure adjustment device the second specific fluid pressure within the supply volume is adjusted (i) at least during the measurement period and / or time-dependently and / or (ii) in such a way that at least at least one, preferably at each, measurement time, the, in particular current, fluid pressure within the supply volume is different from at least the first specific fluid pressure set at the respective measurement time and / or the fluid pressure existing in the chamber at the respective measurement time.

[0012] The invention is therefore based on the surprising finding that a particularly reliable and accurate non-invasive blood pressure measurement, in particular including a pulse wave analysis, can be carried out if the available measuring range of the differential pressure sensor is used as completely as possible for the detection of the pressure changes caused by the pulse waves of the living being in the chamber of the compression device.

[0013] By measuring the fluid pressure in the chamber against the fluid pressure in the supply volume, the required measuring range of the sensor can be reduced by adjusting the fluid pressure in the supply volume. At the same time, a larger portion of the measuring range of the differential pressure sensor is available for detecting the pressure changes caused by the pulse waves. Due to the lower measuring range requirements, for example, due to the reduced maximum pressure that the sensor must be able to detect, less expensive differential pressure sensors can also be used. Higher resolutions can also be achieved for a sensor with a smaller measuring range at the same cost.This is because the bits of an analog / digital (AD) converter used, which, for example, converts an (analog) voltage signal supplied by the differential pressure sensor as a function of the pressure difference into a digital signal, are then available for a reduced range of values.

[0014] Those skilled in the art will understand that during non-invasive blood pressure measurement, time-dependent pressure waves propagate across the blood vessel walls of the living being due to the living being's heartbeat, thereby exerting time-dependent forces on the compression device and thus on the chamber. These forces lead to a time-dependent change in volume in the chamber and thus contribute to a time-dependent change in the fluid pressure of the fluid in the chamber. The acting forces, and thus the pressure conditions within the chamber, can depend on, and advantageously also do depend on, the pressure with which the compression device acts on the part of the living being's body. Based on the course of the pressure changes caused by the pulse waves within the chamber for various external pressures of the compression device, blood pressure parameters can advantageously be determined in an at least partially known manner.

[0015] For example, when performing a conventional oscillatory measurement, the pulse waves typically cause a pressure difference of 2.5 mmHg at the peak in a healthy human and between 0.9 and 2.5 mmHg throughout the entire evaluation, and between 0.22 and 0.9 mmHg in a healthy cat, in the compression device chamber when typical fluid pressures are built up in the chamber. These fluid pressures (i.e., the first specific fluid pressure) generally range from above 130 mmHg to below 80 mmHg in measurements on humans, and from 300 mmHg to 10 mmHg in a cat, for example.

[0016] By measuring the fluid pressure in the chamber against the fluid pressure in the pre-filled volume rather than against the atmosphere, as proposed, the measuring range of the sensor (such as a differential pressure sensor, which is preferably used for this purpose) does not need to be designed for the maximum pressures occurring in the chamber. The required measuring range is preferably determined based on the difference between the first and second specific fluid pressures and the typical pressure changes in the chamber due to the pulse waves. Thus, the value range detectable by the sensor can be reduced to, for example, 50 mmHg (in humans) and 10 mmHg (in a cat).

[0017] At the same time, the bits (approximately 8 bits) of the A / D converter used are then available for a smaller value range. Thus, if the value range to be recorded with the pressure sensor can be reduced from 0..150 mmHg to 0..50 mmHg, the resolution is improved from 0.586 mmHg / bit (150 mmHg / 256 bits = 0.586 mmHg / bit) to 0.195 mmHg / bit (50 mmHg / 256 bits = 0.195 mmHg / bit) using the same 8-bit A / D converter.

[0018] This allows sensors with a significantly smaller measuring range to be used while still obtaining even greater information content. This also saves costs, as sensors with a smaller measuring range are often less expensive. The sensor only needs to be designed for significantly smaller amplitude values. At the same time, reducing the measuring range allows for increased resolution at the same or even lower cost.

[0019] For example, the number of bits can be reduced while maintaining the same resolution, which advantageously allows an increase in the sampling rates, i.e. the recording rates of successive measured values.

[0020] The proposed method thus makes it possible to record, with significantly lower economic effort and even with improved accuracy, especially pulse waves from living beings which cause pressure changes in the chamber in the range of only sub-mmHg, as is typically the case with many living beings, such as cats (pressure changes here are in the range of only pHg, for example).

[0021] The proposed method thus makes it possible to change, in particular shift and / or tilt, the baseline of the pulse waves (at least notionally) (compared to a pressure measurement against the atmosphere). This makes the method very flexible.

[0022] In this context, the inventors primarily recognized that the proposed method makes it very easy to align the pressure fluctuations caused by the pulse waves in such a way that the pressure values ​​of the pulse waves are oriented around the zero line, preferably symmetrically. Thus, the pulse wave pattern covers both positive and negative pressure values. This allows the use of an A / D converter that is also designed for negative values. This allows this value range to be utilized particularly well and is not lost. The method thus enables the flexible use of different A / D converters.

[0023] Furthermore, the method advantageously allows the pulse waves to be recorded in a mirrored pattern along a line, particularly a horizontal one. For this purpose, it is sufficient, and is also implemented in a preferred embodiment, to calculate the differential value by subtracting the fluid pressure in the chamber from the fluid pressure in the supply volume. This can be achieved particularly easily by appropriately connecting both sides of a differential pressure sensor to the chamber and the supply volume.

[0024] Preferably, the positioning of the baseline and / or orientation (in particular in the form of a mirror image) of the pulse waves can be influenced by the selection of the second specific fluid pressure in the supply volume, by the selection of whether the second specific fluid pressure in the supply volume is greater or lesser than the first specific fluid pressure in the chamber and / or by the selection of how the difference between the fluid pressures in the chamber and the supply volume is formed, i.e. whether the fluid pressure in the supply volume is subtracted from the fluid pressure in the chamber or whether the fluid pressure in the chamber is subtracted from the fluid pressure in the supply volume.

[0025] Furthermore, the inventors discovered that undefined pressure values ​​were recorded due to interference, such as the activation of the valves and / or pumps used to adjust the first specific fluid pressure in the chamber, or a temporary muscle relaxation or twitching of the subject and the resulting pressure change in the chamber. By adjusting the baseline in this case, it can be advantageously ensured that the differential pressure sensor and / or the A / D converter is or will be operated within a permissible value range. This allows artifacts during measurement data recording to be reliably detected and evaluated.

[0026] Preferably, the fluid pressure in the chamber (in particular, at least during the measurement period) is determined by several influences. The fluid pressure in the chamber is advantageously determined at least by the time-dependent first specific fluid pressure and a time-dependent volume change within the chamber caused by the pulse waves. The time-dependent volume change advantageously represents the pulse waves (which propagate across the blood vessel walls with each heartbeat), which are thus measurable as pressure variations and can be represented, at least conceptually, as superimposed on the first specific fluid pressure.

[0027] The fluid pressure in the chamber can therefore advantageously be represented as a composition (in particular as an additive superposition) of the first specific fluid pressure and the pressure changes due to the pulse waves. In other words, the time-dependent pressure changes due to the pulse waves are thus imposed on the profile of the first specific fluid pressure. Indeed, the profile of the first specific fluid pressure can advantageously be derived from the profile of the fluid pressure in the chamber (in particular at least during the measurement period and / or measured against atmosphere) as a (for example, falling) "baseline" of the pulse waves.

[0028] The fluid pressure in the chamber at a specific point in time (i.e. the current fluid pressure) is then advantageously influenced by at least the first specific fluid pressure and the volume change of the chamber as a result of the influence of the pulse waves at that point in time.

[0029] Preferably, the contribution to the fluid pressure within the chamber which can be changed by means of the first pressure adjustment device is referred to as the first specific fluid pressure.

[0030] Preferably, the contribution to the fluid pressure within the supply volume which can be changed by means of the second pressure adjustment device is referred to as the second specific fluid pressure.

[0031] In one embodiment, the method for non-invasive blood pressure measurement may be or include a method for pulse wave analysis and / or pulse wave recording.

[0032] The time-varying pressure exerted on the body part during the measurement period can change continuously in preferred embodiments. However, it can also be preferred for the time-varying pressure exerted on the body part during the measurement period to be constant, at least temporarily. This advantageously makes it possible to record measured values ​​at a constant applied pressure. Thus, for example, the pulse waves can be recorded and / or analyzed at a constant applied pressure. In the present application, the respective pressures are specified in the unit mmHg (millimeters of mercury), which is customary in the field of blood pressure measurement. If reference is made to very low pressure values, the unit p.Hg (1 mmHg = 1000 p.Hg) is also sometimes used.

[0033] It is clear to those skilled in the art that the (individual) pulse wave propagating from the heart through the blood vessels can vary depending on its location in the body and, for example, is also influenced at the measurement location by the pressure exerted on the body part by the compression device. In the present application, however, the measured profile of the pressure changes caused by the (multiple consecutive) pulse waves is sometimes referred to as a pulse wave itself. However, those skilled in the art will understand from the respective context whether the actual (individual or multiple consecutive) pulse wave(s) emanating from the heart is meant, or whether the profile of the pressure differences occurring in the chamber over several heartbeats is meant.Pulse waves recorded over several heartbeats typically have several (local) amplitudes, which were preferably recorded at at least partially different pressures acting on the body part, and based on whose magnitude, for example, blood pressure parameters can be determined.

[0034] In the present application, unless otherwise indicated by the context, the width of a (pressure) value range is preferably understood as the difference between the maximum and minimum (pressure) values ​​within this (pressure) value range. The (pressure) value range 80 mmHg to 130 mmHg therefore has a width of 50 mmHg (130 mmHg - 80 mmHg).

[0035] Preferably, in the present application, unless otherwise indicated by the respective context, the differential pressure AP between a first pressure P1 and a second pressure P2 is measured as AP = P1-P2. Therefore, if the first pressure is greater than the second pressure, the differential pressure AP assumes positive values. And if the second pressure is greater than the first pressure, the differential pressure AP assumes negative values. Optionally, in embodiments, the differential pressure can also be defined as AP = P2-P1, in which case the opposite signs apply.

[0036] Preferably, the chamber and the supply volume are fluidically separated from each other, particularly at least during the measurement period. This advantageously ensures that the fluid pressure in the supply volume is not influenced by the fluid pressure in the chamber. In this way, the fluid pressure in the supply volume can serve as a particularly reliable comparison value, and the pulse waves can be recorded very precisely.

[0037] The measurement period can be defined or definable. For example, the measurement period is more than 10 seconds, less than 600 seconds, and / or between 10 seconds and 600 seconds. Preferably, the measurement period is 30 seconds or more, 60 seconds or more, and / or 120 seconds or more. Particularly preferred measurement periods are between 10 and 30 seconds or between 30 and 60 seconds. Alternatively or additionally, the measurement period can advantageously be defined by a period within which the differential pressure measurements relevant for blood pressure measurement occur.

[0038] In one embodiment, the measurement period is selected at least partially depending on the living being's pulse rate. For this purpose, the living being's pulse rate is optionally determined.

[0039] The differential pressure measured at a given measurement time is advantageously the pressure difference between the current fluid pressures in the chamber and the supply volume at that time. The chamber is preferably provided within the compression device.

[0040] Preferably, the compression device and / or the chamber are deformable at least in some regions and / or are designed such that the volume within the chamber (and thus the fluid pressure in the chamber) can be changed by applying a force (in particular due to the pulse waves) to the compression device. For example, this can be particularly advantageously implemented by the compression device being a blood pressure cuff. Therefore, the compression device is advantageously a blood pressure cuff or comprises one. The chamber can then be provided in the cuff and have a volume enclosed within the cuff.

[0041] Preferably, the chamber has a volume within which the fluid pressure exists and / or within which the first specific fluid pressure is adjustable. The chamber can be provided within a blood pressure cuff. In this case, the chamber and the volume can be provided with the cuff in a conventional manner.

[0042] The first pressure adjustment device preferably comprises a first pressure sensor. This first pressure sensor preferably measures the respective fluid pressure in the chamber relative to atmosphere. In one embodiment, the first pressure sensor is used to monitor and / or regulate the fluid pressure, in particular the first specific fluid pressure, in the chamber.

[0043] The second pressure adjustment device preferably comprises a second pressure sensor. This second pressure sensor preferably measures the respective fluid pressure in the supply volume relative to atmosphere. In one embodiment, the second pressure sensor is used to monitor and / or regulate the fluid pressure, in particular the second specific fluid pressure, in the supply volume.

[0044] In one embodiment, the setting of the pressure difference between the first and second specific fluid pressures, so that at least at each measuring time the fluid pressure within the supply volume is different from at least the first specific fluid pressure set at the respective measuring time, comprises the inclusion of values ​​from the first pressure sensor, the second pressure sensor and / or the differential pressure sensor, in particular being processed within the framework of a control and / or regulation.

[0045] In one embodiment, a computing unit can be provided that is operatively connected to one or both pressure adjustment devices in order to be able to appropriately influence, monitor, control, and / or regulate them. In this way, the first specific fluid pressure in the chamber and / or the second specific fluid pressure in the supply volume can be reliably adjusted (and as described above).

[0046] The fluid in the chamber and / or in the storage volume can advantageously be air.

[0047] The measurement period can advantageously be defined or definable in terms of its length.

[0048] For example, the measured values ​​can be recorded at a rate of at least 10 per second, at most 10,000 per second, and / or between 10 and 10,000 per second. Preferred recording rates are between 10 and 100 per second, 100 and 500 per second, 300 and 800 per second, 500 and 1,000 per second, and / or 800 and 1,500 per second. Particularly preferred are recording rates of 10 per second, 100 per second, 500 per second, and / or 1,000 per second. As already mentioned above, the proposed method also allows for comparatively high recording rates, thus enabling meaningful blood pressure tests.

[0049] In one embodiment, the acquisition rate of the measured values ​​is selected, at least in part, depending on the subject's pulse rate. For this purpose, the subject's pulse rate is optionally determined. This advantageously ensures that every pulse wave emanating from the heart is detected.

[0050] In one embodiment, the individual measured values ​​are recorded at equal time intervals. The inverse recording rate then represents the time interval between two measured values.

[0051] The living being can be, for example, a human being or an animal, such as a mammal, for example a dog, a cat, a hamster, a mouse, a horse, a hare, a rabbit or a rat, a bird, a reptile or an amphibian.

[0052] The part of the body of the living being can, for example, be blood-carrying and / or an extremity of the living being, in particular an extremity with blood flow, such as an upper arm of a human being or a tail of an animal.

[0053] In one embodiment, the second specific fluid pressure within the supply volume is adjusted by means of the second pressure adjustment device in such a way that at least at each measuring time the, in particular current, fluid pressure within the supply volume is also different from the ambient pressure.

[0054] The individual components for non-invasive blood pressure measurement, i.e. in particular compression device, first pressure adjustment device, second pressure adjustment device and / or means for recording the differential pressure (such as a differential pressure sensor), can advantageously be provided by a device for non-invasive blood pressure measurement and / or be provided individually and / or together for the method.

[0055] Alternatively or additionally, it can also be provided that the first specific fluid pressure within the chamber is set, in particular by means of the first pressure adjustment device and / or before the measuring period, to a first initial pressure value, which is preferably above the systolic blood pressure of the living being, and preferably the first specific fluid pressure is changed in a time-dependent manner starting from the first initial pressure value, in particular at least during the measuring period, preferably until a first target pressure value, which is preferably below the diastolic blood pressure of the living being, is reached.

[0056] This allows for a very precise, non-invasive blood pressure measurement to be performed under known conditions. In particular, this also enhances repeatability, allowing for particularly advantageous comparisons of different measurements. This allows for reliable detection of deviations between two measurements that could indicate a disease in the patient.

[0057] The first initial pressure value can be defined or definable. The first target pressure value can be defined or definable.

[0058] Preferably, the first specific fluid pressure is changed in a time-dependent manner starting from the first initial pressure value from a point in time which is before the beginning of the measuring period or which represents the beginning of the measuring period.

[0059] Preferably, the first specific fluid pressure reaches the first target pressure value at a time that is after the end of the measurement period or that represents the end of the measurement period. For example, the first initial pressure value may be based on the systolic blood pressure and be above this value, and / or the first target pressure value may be based on the diastolic blood pressure and be below this value.

[0060] For example, the first initial pressure value may be based on the diastolic blood pressure and be below this value and / or the first target pressure value may be based on the systolic blood pressure and be above this value.

[0061] For example, the chamber may first be inflated until the first specific fluid pressure has reached the first initial pressure value (which may take into account the exemplary values ​​mentioned above) and then the first specific fluid pressure may be changed until the defined or definable first target pressure value (which may take into account the exemplary values ​​mentioned above) is reached.

[0062] For example, it can be provided that while the first specific fluid pressure is brought to the first initial pressure value, the fluid pressure, in particular the first specific fluid pressure, in the chamber is monitored by means of the first pressure sensor and / or the first specific fluid pressure is regulated.

[0063] For example, it can be provided that while the first specific fluid pressure is changed to the first target pressure value, the fluid pressure, in particular the first specific fluid pressure, in the chamber is monitored by means of the first pressure sensor and / or the first specific fluid pressure is regulated.

[0064] In a preferred embodiment, the first specific fluid pressure set at the first measuring time during the measuring period is lower or higher than the first initial pressure value. In other words, the measuring period can be timed so that it only begins after the first specific fluid pressure has already been changed starting from the first initial pressure value. This is particularly preferred because, during the period up to the first measuring time, any control electronics used can advantageously adjust themselves. Likewise, alternatively or additionally, the first specific fluid pressure set at the last measuring time during the measuring period can also be higher or lower than the first target pressure value.

[0065] Alternatively or additionally, it can also be provided that (A) the first initial pressure value (i) is greater than 10 mmHg, preferably greater than 50 mmHg, preferably greater than 100 mmHg, preferably greater than 150 mmHg, preferably greater than 200 mmHg, preferably greater than 250 mmHg, preferably greater than 300 mmHg, preferably greater than 350 mmHg, preferably greater than 400 mmHg, preferably greater than 450 mmHg, preferably greater than 500 mmHg, (ii) is less than 700 mmHg, preferably less than 600 mmHg, preferably less than 550 mmHg, preferably less than 500 mmHg, preferably less than 450 mmHg, preferably less than 400 mmHg, preferably less than 350 mmHg, preferably less than 300 mmHg, preferably less than 250 mmHg, preferably less than than 200 mmHg, preferably less than 150 mmHg, preferably less than 100 mmHg, preferably less than 50 mmHg, and / or (iii) between 10 mmHg and 700 mmHg, preferably between 100 mmHg and 500 mmHg,preferably between 100 mmHg and 400 mmHg, preferably between 150 mmHg and 350 mmHg, preferably between 150 mmHg and 200 mmHg or between 200 mmHg and 350 mmHg, and / or,

[0066] (B) the first target pressure value (i) greater than 1 mmHg, preferably greater than 3 mmHg, preferably greater than 5 mmHg, preferably greater than 10 mmHg, preferably greater than 20 mmHg, preferably greater than 30 mmHg, preferably greater than 40 mmHg, preferably greater than 50 mmHg, preferably greater than 60 mmHg, preferably greater than 70 mmHg, preferably greater than 100 mmHg, (ii) less than 300 mmHg, preferably less than 250 mmHg, preferably less than 200 mmHg, preferably less than 150 mmHg, preferably less than 100 mmHg, preferably less than 80 mmHg, preferably less than 50 mmHg, preferably less than 30 mmHg, preferably less than 20 mmHg, preferably less than 15 mmHg, preferably less than 10 mmHg, preferably less than 5 mmHg, preferably less than 3 mmHg, and / or (iii) between 1 mmHg and 300 mmHg, preferably between 1 mmHg and 200 mmHg, preferably between 1 mmHg and 100 mmHg, preferably between 1 mmHg and 80 mmHg,preferably between 1 mmHg and 20 mmHg or between 20 mmHg and 80 mmHg.

[0067] Alternatively or additionally, it can also be provided that the first specific fluid pressure, in particular at least during the measuring period, is changed continuously or stepwise by means of the first pressure adjustment device.

[0068] A continuous change of the first specific fluid pressure can be achieved, for example, by continuously removing the fluid from the chamber or pumping it into the chamber.

[0069] Preferably, a step-by-step change in the first specific fluid pressure is understood to mean a curve of the first specific fluid pressure which repeatedly, in particular periodically, at least temporarily remains at a constant pressure level and wherein between two immediately successive pressure levels, a first and an immediately following second pressure level, the first specific fluid pressure changes from the first pressure level to the second pressure level, in particular at least temporarily in a straight line and / or at least temporarily according to a curved curve.

[0070] Alternatively or additionally, it can also be provided that the first specific fluid pressure, in particular at least during the measuring period, is changed at a, in particular continuous, rate of change of (i) 1 mmHg or more than 1 mmHg per second, (ii) 50 mmHg or less than 50 mmHg per second, preferably 30 mmHg or less than 30 mmHg per second, preferably 20 mmHg or less than 20 mmHg per second, and / or (iii) between 1 mmHg and 50 mmHg per second, preferably between 3 mmHg per second and 30 mmHg per second.

[0071] Preferred rates of change are 1 mmHg per second, 3 mmHg per second, 5 mmHg per second, 10 mmHg per second, 15 mmHg per second, 20 mmHg per second, 25 mmHg per second and / or 27 mmHg per second.

[0072] If the living being is a human, a rate of change of between 3 mmHg and 27 mmHg per second is particularly preferred.

[0073] In one embodiment, the rate of change is selected at least partially as a function of the living being's pulse rate. For this purpose, the living being's pulse rate is optionally determined. This advantageously allows every pulse wave emanating from the heart to be detected.

[0074] Alternatively or additionally, it can also be provided that the first specific fluid pressure, in particular at least during the measuring period, is changed at a stepwise rate of change of (i) 1 mmHg or more than 1 mmHg, (ii) 50 mmHg or less than 50 mmHg, and / or (iii) between 1 mmHg and 50 mmHg.

[0075] The rate of change is preferably to be regarded as the pressure difference between two of the immediately successive pressure levels described above.

[0076] Preferred rates of change are 1 mmHg, 3 mmHg, 5 mmHg, 10 mmHg, 15 mmHg, 20 mmHg, 25 mmHg, and / or 27 mmHg. Alternatively or additionally, it can also be provided that the time-dependent change in the first specific fluid pressure comprises or represents the time-dependent reduction of the first specific fluid pressure.

[0077] For example, the first specific fluid pressure may be reduced from the first initial pressure value to the first target pressure value.

[0078] Alternatively or additionally, it can also be provided that the time-dependent change of the first specific fluid pressure comprises or represents the time-dependent increase of the first specific fluid pressure.

[0079] For example, the first specific fluid pressure may be increased from the first initial pressure value to the first target pressure value.

[0080] Alternatively or additionally, it can also be provided that, in particular at least during the measuring period, the fluid pressure existing in the chamber at least at individual measuring times, in particular the current fluid pressure, results at least from the time-dependent first specific fluid pressure and a time-dependent impact pressure exerted on the chamber by the part of the body of the living being, wherein the impact pressure is preferably influenced at least partially and / or at least temporarily by the blood pressure of the living being and / or by pulse waves propagating via the blood vessels of the living being.

[0081] In other words, the fluid pressure measurable in the chamber (i.e. the current fluid pressure) is influenced by several factors.

[0082] One of at least two factors is preferably the pressure increase caused by the first pressure adjustment device according to the first specific fluid pressure relative to atmosphere. Another factor of the at least two factors is preferably the forces ultimately mediated by the living being's pulse rate, which act on the compression device and thus on the chamber via the pulse waves, which lead to a change in volume in the chamber and thus to a change in the fluid pressure of the fluid in the chamber according to the course of the pulse waves.

[0083] It may, of course, be the case that the factors cannot be separated from one another, at least based on a single measured value of the fluid pressure in the chamber relative to the atmosphere. However, for example, especially if the course of the fluid pressure in the chamber were recorded over time, the pulse waves could follow an (imaginary) pressure curve corresponding to the first specific fluid pressure.

[0084] Alternatively or additionally, it can also be provided that the second specific fluid pressure within the supply volume, in particular by means of the second pressure adjustment device and / or before the measuring period, is set to a second initial pressure value and / or, in particular starting from the second initial pressure value and / or at least during the measuring period, is changed in a time-dependent manner, preferably until a second target pressure value is reached.

[0085] Preferably, the second specific fluid pressure is changed in a time-dependent manner starting from the second initial pressure value from a point in time which is before the beginning of the measuring period or which represents the beginning of the measuring period.

[0086] Preferably, the second specific fluid pressure reaches the second target pressure value at a time which is after the end of the measuring period or which represents the end of the measuring period.

[0087] The second initial pressure value can be defined or definable. The second target pressure value can be defined or definable. For example, the prefilled volume can first be inflated until the second specific fluid pressure reaches the second initial pressure value, and then the second specific fluid pressure can be changed until the defined or definable second target pressure value is reached.

[0088] For example, it can be provided that while the second specific fluid pressure is brought to the second initial pressure value, the fluid pressure, in particular the second specific fluid pressure, in the supply volume is monitored by means of the second pressure sensor and / or the second specific fluid pressure is regulated.

[0089] For example, it can be provided that while the second specific fluid pressure is changed to the second target pressure value, the fluid pressure, in particular the second specific fluid pressure, in the supply volume is monitored by means of the second pressure sensor and / or the second specific fluid pressure is regulated.

[0090] In a preferred embodiment, the second specific fluid pressure set at the first measuring time during the measuring period is lower or higher than the second initial pressure value. In other words, the measuring period can be timed so that it only begins after the second specific fluid pressure has already been changed starting from the second initial pressure value. This is particularly preferred because any control electronics used can thus advantageously adjust themselves during the period up to the first measuring time. Likewise, alternatively or additionally, the second specific fluid pressure set at the last measuring time during the measuring period can be higher or lower than the second target pressure value.

[0091] In a likewise preferred embodiment, it can be provided: (i) The first specific fluid pressure, in particular while the fluid pressure, in particular the first specific fluid pressure, in the chamber is monitored and / or regulated by means of the first pressure sensor, is brought to the first initial pressure value or a fluid pressure deviating therefrom by at most 50%, preferably by at most 40%, preferably by at most 30%, preferably by at most 20%, preferably by at most 10%, preferably by at most 5%, preferably by at most 3%, preferably by at most 1%, and / or the second specific fluid pressure, in particular while the fluid pressure, in particular the second specific fluid pressure, in the supply volume is monitored and / or regulated by means of the second pressure sensor, is brought to the second initial pressure value or one of these by at most 50%, preferably by at most 40%, preferably by at most 30%, preferably by at most 20%,preferably by a maximum of 10%, preferably by a maximum of 5%, preferably by a maximum of 3%, preferably by a maximum of 1%, different fluid pressure and / or (ii) a defined or definable pressure difference between the fluid pressure within the chamber and the fluid pressure within the supply volume is set, in particular subsequently and / or during this time, by a control system taking into account measured values ​​of the differential pressure sensor.

[0092] A fluid pressure preferably deviates from an initial pressure value by a maximum of X% if the ratio of "fluid pressure in mmHg" and "initial pressure value in mmHg" is between lX / 100 and l+X / 100.

[0093] In other words, one of the two fluid pressures within the chamber and the supply volume, or both fluid pressures, can be adjusted to an approximate value. A low-cost pressure sensor can be used for this purpose, as a comparatively low resolution is sufficient. The pressure difference between the chamber and the supply volume can then be adjusted to the desired value using the much finer-resolution differential pressure sensor. Alternatively or additionally, it can also be provided that (A) the second initial pressure value (i) is greater than 10 mmHg, preferably greater than 50 mmHg, preferably greater than 100 mmHg, preferably greater than 150 mmHg, preferably greater than 200 mmHg, preferably greater than 250 mmHg, preferably greater than 300 mmHg, preferably greater than 350 mmHg, preferably greater than 400 mmHg, preferably greater than 450 mmHg, preferably greater than 500 mmHg, (ii) less than 700 mmHg, preferably less than 600 mmHg,preferably less than 550 mmHg, preferably less than 500 mmHg, preferably less than 450 mmHg, preferably less than 400 mmHg, preferably less than 350 mmHg, preferably less than 300 mmHg, preferably less than 250 mmHg, preferably less than 200 mmHg, preferably less than 150 mmHg, preferably less than 100 mmHg, preferably less than 50 mmHg, and / or (iii) between 10 mmHg and 700 mmHg, preferably between 100 mmHg and 500 mmHg, preferably between 100 mmHg and 400 mmHg, preferably between 150 mmHg and 350 mmHg, preferably between 150 mmHg and 200 mmHg or between 200 mmHg and 350 mmHg, and / or,

[0094] (B) the second target pressure value (i) greater than 1 mmHg, preferably greater than 3 mmHg, preferably greater than 5 mmHg, preferably greater than 10 mmHg, preferably greater than 20 mmHg, preferably greater than 30 mmHg, preferably greater than 40 mmHg, preferably greater than 50 mmHg, preferably greater than 60 mmHg, preferably greater than 70 mmHg, preferably greater than 100 mmHg, (ii) less than 300 mmHg, preferably less than 250 mmHg, preferably less than 200 mmHg, preferably less than 150 mmHg, preferably less than 100 mmHg, preferably less than 80 mmHg, preferably less than 50 mmHg, preferably less than 30 mmHg, preferably less than 20 mmHg, preferably less than 15 mmHg, preferably less than 10 mmHg, preferably less than 5 mmHg, preferably less than 3 mmHg, and / or (iii) between 1 mmHg and 300 mmHg, preferably between 1 mmHg and 200 mmHg, preferably between 1 mmHg and 100 mmHg, preferably between 1 mmHg and 80 mmHg,preferably between 1 mmHg and 20 mmHg or between 20 mmHg and 80 mmHg.

[0095] This allows the fluid pressure within the supply volume to be very reliably adjusted and / or changed over time.

[0096] Alternatively or additionally, it can also be provided that the second specific fluid pressure, in particular at least during the measurement period, within the supply volume (i) is adjusted such that the ratio of the first specific fluid pressure in the chamber and the second specific fluid flow within the supply volume, in particular at each measurement time, has a value (a) of between 0.5 and less than 1.0, in particular of between 0.6 and less than 1.0, in particular of between 0.7 and less than 1.0, in particular of between 0.9 and less than 1.0, and / or (b) of between more than 1.0 and 1.5, in particular of between more than 1.0 and 1.4, in particular of between more than 1.0 and 1.3, in particular of between more than 1.0 and 1.1, (ii) is changed at least temporarily simultaneously with the first specific fluid pressure within the chamber, (iii) is changed in phase with the first specific fluid pressure within the chamber,(iv) has a pressure difference relative to the first specific fluid pressure within the chamber of at least one, preferably at least two, preferably at least three, preferably at least four, preferably at least five times the maximum pressure change caused by the pulse waves during the measurement period, and / or (v) is changed at an identical rate of change as the first specific fluid pressure within the chamber. The two fluid pressures are preferably changed in phase when an increase in the fluid pressure in the chamber is counteracted by an increase in the fluid pressure in the supply volume, or vice versa.and when a decrease in the fluid pressure in the chamber is counteracted by a decrease in the fluid pressure in the supply volume, or vice versa. The fluid pressure in the chamber and the supply volume can be changed simultaneously or in phase, in particular by adjusting the first specific fluid pressure and / or the second specific fluid pressure.

[0097] Preferably, an identical rate of change of the fluid pressures is present when the two rates of change differ from each other by at most 10%, preferably at most 7%, preferably at most 5%, preferably at most 3%, preferably at most 2%, preferably at most 1%, preferably at most 0.5%.

[0098] Alternatively or additionally, it can also be provided that, in particular at least at the individual measuring times, the pressure difference between the first specific fluid pressure within the chamber and the second specific fluid pressure within the supply volume is set (i) to a constant value and / or (ii) to a value of (a) 1 mmHg or more than 1 mmHg, (b) 600 mmHg or less than 600 mmHg and / or (c) between 1 mmHg and 600, preferably between 1 mmHg and 100 mmHg, preferably between 10 mmHg and 50 mmHg, such as for example 1 mmHg, 10 mmHg, 25 mmHg, 30 mmHg or 50 mmHg.

[0099] Advantageous pressure differences have values ​​of, for example, 25 mmHg, 50 mmHg or 100 mmHg.

[0100] A constant pressure difference here preferably means that the same pressure difference exists between the first specific fluid pressure in the chamber and the second specific fluid pressure in the supply volume, in particular at each measurement time. In this case, either the first specific fluid pressure in the chamber can be greater than the second specific fluid pressure in the supply volume, or conversely, the first specific fluid pressure in the chamber can be lower than the second specific fluid pressure in the supply volume.

[0101] In one embodiment, setting the constant pressure difference comprises taking into account values ​​of the first pressure sensor, the second pressure sensor and / or the differential pressure sensor, in particular processing them within the scope of a control and / or regulation.

[0102] Alternatively or additionally, it can also be provided that the, in particular current, fluid pressure within the supply volume is not influenced by the living being or parts thereof, in particular not by the blood pressure of the living being and / or by pulse waves propagating via the blood vessels of the living being.

[0103] Preferably, the storage volume is therefore provided and / or arranged in such a way that it is not in operative connection with the living being, in particular, it is not arranged on the living being and / or is not in contact with it. For example, the storage volume can be provided separately and / or spatially separated from the living being.

[0104] In one embodiment, the fluid pressure in the reservoir volume, in particular for given ambient conditions, such as in particular a given atmospheric pressure, is determined only by the second specific fluid pressure.

[0105] Alternatively or additionally, it can also be provided that the first specific fluid pressure in the chamber and the second specific fluid pressure in the supply volume, in particular at least during the measurement period and / or at least for each measurement, are controlled and / or adjusted in such a way that, in particular at least during the measurement period and / or at least for each measurement, the first specific fluid pressure, preferably at any time, is at a greater or smaller value than the second specific fluid pressure.

[0106] In one embodiment, the first specific fluid pressure within the chamber and the second specific fluid pressure within the supply volume are each set to the first and second initial pressure values, respectively, which, however, differ, and starting from the respective initial pressure value, the first specific fluid pressure within the chamber and the second specific fluid pressure within the supply volume are changed simultaneously and / or at an identical rate of change, i.e., for example, reduced or increased, wherein, for example, the pressure difference between the first specific fluid pressure and the second specific fluid pressure is always kept constant.

[0107] Alternatively or additionally, it can also be provided that the recorded measured values ​​describe a measurement curve which represents and / or depicts and / or makes it possible to determine a course of the pulse waves of the blood pressure of the living being.

[0108] For example, a curve can be placed through the measured values ​​according to the least squares method in order to obtain a measurement curve and / or the course of the pulse waves.

[0109] Alternatively or additionally, it may also be provided that the recorded measured values ​​are evaluated and / or parameters of the blood pressure, such as the systolic blood pressure, the diastolic blood pressure and / or morphological properties, of the living being are determined based on at least one result of the evaluation.

[0110] In one embodiment, the evaluation of the measured values ​​comprises determining and evaluating an envelope for the measured values, and determining the parameters of the blood pressure based on at least one result of the evaluation of the envelope.

[0111] The evaluation of the envelope can be carried out in a manner known per se. For example, the envelope of measured values ​​recorded during a decreasing first specific fluid pressure can rise at a first specific fluid pressure (here, the distinction is made between presystolic pulse pressure amplitude when the artery is closed and the first opening of the artery), with this first specific fluid pressure preferably then representing the systolic blood pressure of the subject, reach its maximum at a second specific fluid pressure, with this second specific fluid pressure preferably then representing the mean arterial pressure (MAP) of the subject, and fall again at a third specific fluid pressure, with this third specific fluid pressure preferably then representing the diastolic blood pressure of the subject.

[0112] In this way, the blood pressure parameters mentioned can be determined particularly advantageously based on the recorded measured values ​​and / or the envelope.

[0113] Preferably, the amplitudes of the individual pulse waves are evaluated and, if possible, compared with each other. This allows for particularly advantageous detection of morphological changes in the amplitudes and pulse waves.

[0114] In one embodiment, the recorded measured values, in particular the course of the pulse waves, the parameters of the blood pressure and / or at least one result of the evaluation are output graphically, for example on a display device.

[0115] Morphological characteristics of the organism can include one or more of the following options: pulse pressure, amplitude volume, beat-to-beat pulse spacing, amplitude width and height, and / or respiration. In one embodiment, the measured values ​​are evaluated with the computing unit as described above.

[0116] Alternatively or additionally, it can also be provided that the differential pressure between the, in particular current, fluid pressure in the chamber and the, in particular current, fluid pressure in the supply volume is measured by means of a differential pressure sensor, wherein preferably a first side of the differential pressure sensor is fluidly connected to the chamber and a second side of the differential pressure sensor is fluidly connected to the supply volume and in particular the differential pressure sensor supplies positive pressure values ​​when the, in particular current, fluid pressure in the chamber is greater than the, in particular current, fluid pressure in the supply volume, and the differential pressure sensor supplies negative pressure values ​​when the, in particular current, fluid pressure in the chamber is smaller than the, in particular current, fluid pressure in the supply volume.

[0117] Advantageously, the first side of the differential pressure sensor is subjected to the fluid pressure within the chamber and / or the second side of the differential pressure sensor is subjected to the fluid pressure within the supply volume.

[0118] Preferably, the differential pressure sensor has a measuring range which corresponds to at least one time, preferably at least two times, preferably at least three times, preferably at least four times, preferably at least five times, the expected width of the value range of the pulse waves of the living being.

[0119] For example, the differential pressure sensor may have a measuring range of at least 10 mmHg or of at least 30 mmHg or of at least 50 mmHg.

[0120] It can advantageously be provided that the computing unit is in operative connection with the differential pressure sensor and / or that the computing unit receives the measured values ​​from it.

[0121] Alternatively or additionally, it can also be provided that the first pressure adjustment device has a first electronic valve and / or a first pump, such as a piezo pump, and / or wherein the time-dependent change of the first specific fluid pressure comprises controlling and / or regulating the first electronic valve and / or the first pump in a time-dependent manner.

[0122] A corresponding valve and / or pump can be regulated and / or controlled particularly reliably and inexpensively.

[0123] Alternatively or additionally, it can also be provided that the second pressure adjustment device has a second electronic valve and / or a second pump, such as a piezo pump, and / or wherein the time-dependent change of the second specific fluid pressure within the supply volume comprises controlling and / or regulating the second electronic valve and / or the second pump in a time-dependent manner.

[0124] A corresponding valve and / or pump can be regulated and / or controlled particularly reliably and inexpensively.

[0125] Alternatively or additionally, it can also be provided that the compression device comprises or represents a blood pressure measuring cuff, wherein the part of the body of the living being can preferably be compressed to different degrees by the cuff, and / or wherein the chamber is a chamber of the cuff, in particular one that can be filled and emptied with a fluid.

[0126] In order to perform a non-invasive blood pressure measurement, the method can therefore advantageously provide for the compression device, in particular the blood pressure measurement cuff, to first be placed on the living being, for example by placing it around the living being's extremity. Preferably, the first specific fluid pressure in the chamber is then increased, for example by inflating the chamber with fluid (e.g., air) (for example, using the first pump). This preferably continues until the first specific fluid pressure reaches the first initial pressure value.

[0127] Alternatively or additionally, it can also be provided that the template volume is a volume (i) within an object, (ii) within a hollow body and / or (iii) within a container.

[0128] It has been recognized as particularly advantageous that the size of the supply volume does not have to be based on the size of the chamber volume, since in this case, only the fluid pressures within the chamber and the supply volume are important. Therefore, the size of the supply volume can be selected independently. In principle, a very small volume is also possible, allowing the device used to be particularly compact.

[0129] With a comparatively small volume, only small amounts of fluid must be able to be controlled and / or regulated with sufficient precision to adjust the fluid pressure within the supply volume.

[0130] In order to perform a non-invasive blood pressure measurement, the method can therefore advantageously provide for the second specific fluid pressure in the pre-filled volume to be increased, for example by pumping the pre-filled volume (e.g., within said hollow body) with fluid (e.g., air) (e.g., using the second pump). This preferably continues until the second specific fluid pressure reaches the second initial pressure value.

[0131] The object is achieved by the invention according to a second aspect in that a device for non-invasive blood pressure measurement, comprising a compression device, by means of which a time-varying pressure can be exerted on at least a part of the body of a living being at least during a measuring period, in that a first specific fluid pressure within a chamber of the compression device can be changed in a time-dependent manner at least during the measuring period by means of a first pressure adjustment device provided by the device, wherein the device has a differential pressure sensor and an object with an enclosed storage volume and the device is designed to, at different measuring times during the measuring period, at which at least partially different first specific fluid pressures are set, in each case at least one measured value of a value at the respective measuring time between the,in particular current, fluid pressure within the chamber and the, in particular current, fluid pressure within the supply volume existing differential pressure with the differential pressure sensor, and wherein the device is set up to adapt a second specific fluid pressure within the supply volume by means of a second pressure adaptation device provided by the device, wherein preferably the device is set up to adapt the second specific fluid pressure within the supply volume (i) at least during the measuring period and / or time-dependently and / or (ii) in such a way that at least at least one, preferably at each, measuring time the, in particular current,The fluid pressure within the supply volume is different from at least the first specific fluid pressure set at the respective measurement time and / or the fluid pressure existing in the chamber at the respective measurement time. All advantages described with regard to the method according to the first aspect of the invention also apply accordingly to the device according to the second aspect of the invention. Therefore, reference can be made to the previous explanations in this regard.

[0132] All features, such as in particular physical configurations or relative arrangements of individual parts, described with reference to the method according to the first aspect of the invention can advantageously also be provided in the device, individually and in any combination. Furthermore, the device or its parts are each configured to implement the mandatory method features as well as optionally one or more of the optional method features. Therefore, reference can be made to the previous explanations in this regard.

[0133] In order to carry out the method features, the device can have a computing unit, which computing unit is configured to carry out one or more of the method features, and which computing unit is advantageously operatively connected to one or more other parts of the device in order to be able to suitably influence, monitor, control and / or regulate them (for example, the computing unit can: be operatively connected to one or both pressure adjustment devices and therefore be configured to set the first specific fluid pressure in the chamber and / or the second specific fluid pressure in the supply volume as described above; and / or be operatively connected to the differential pressure sensor and therefore be configured to receive and / or evaluate the measured values ​​therefrom as described above).

[0134] The object is achieved by the invention according to a third aspect in that a housing, in particular for a device for non-invasive blood pressure measurement, such as a device according to the second aspect of the invention, wherein at least one channel system is integrally formed within the housing, wherein preferably at least one specific section of the channel system has a curved course along a main extension of the specific section, is proposed.

[0135] The invention is based on the finding that particularly reliable operation of a device (such as a device for measuring blood pressure) is possible if the fluid lines are predefined and thus better protected against faulty connection or leaks. Because the channel system is formed integrally within the housing in this case, the channel system is protected against tampering with the fluid lines. Since connecting pieces can be dispensed with or at least reduced in number, leaks can also be better prevented. A high level of tightness is particularly advantageous for channel systems that are fluidically connected to volumes and / or form them in which volumes certain fluid pressures are set during blood pressure measurements.

[0136] It was also recognized that the channel system can be formed integrally particularly well by means of 3D printing and that the support material remaining in the cavities of the channel system after the printing process (which may, for example, contain non-solidified particles) can be removed particularly easily and reliably by designing the branches within the channel system to be at least partially curved (instead of, for example, angular).

[0137] This curved design makes it relatively easy to blow the support material out of the duct system by applying compressed air to an opening in the duct system. The same applies to any cleaning work that may be carried out. In curved runs, the compressed air is, in a sense, directed into the duct section adjacent to the curved section. However, if branches are designed in a square shape, the compressed air flow often no longer reaches the duct system, or does not reach as far, particularly into the part of the duct system located downstream of the branch. This means that clearing the duct system of support material and / or cleaning it is not possible, or not reliable, or only possible with considerable effort.

[0138] The specific section of the channel system preferably has an inner diameter of 1 mm or more than 1 mm, preferably of 2 mm or more than 2 mm, preferably of 3 mm or more than 3 mm, preferably of 4 mm or more than 4 mm, preferably of 5 mm or more than 5 mm, preferably of 10 mm or more than 10 mm. Alternatively or additionally, the specific section of the channel system preferably has an inner diameter of 50 mm or less than 50 mm, preferably of 30 mm or less than 30 mm, preferably of 20 mm or less than 20 mm, preferably of 15 mm or less than 15 mm, preferably of 10 mm or less than 10 mm, preferably of 7 mm or less than 7 mm, preferably of 5 mm or less than 5 mm, preferably of 3 mm or less than 3 mm.

[0139] For example, the specific section of the channel system has an inner diameter of between 1 mm and 10 mm, preferably between 1.5 mm and 8 mm, preferably between 2 mm and 5 mm.

[0140] In order to better distinguish it from other canal systems introduced later, the said canal system can also be referred to as a first canal system.

[0141] Alternatively or additionally, it can also be provided that the channel system is at least partially formed, in particular at least the specific section, within a solid housing body.

[0142] This allows the channel system to be particularly well protected, for example against breakage, and the housing as a whole can be made stable.

[0143] Alternatively or additionally, it can also be provided that the housing, the channel system, in particular the specific section, and / or the housing body is at least partially manufactured by means of 3D printing.

[0144] This allows integrally formed structures of the canal system to be implemented easily, cost-effectively and with high precision.

[0145] Alternatively or additionally, it can also be provided that the curved course of the specific section has a radius of curvature which is greater than or equal to half of an inner diameter, in particular half of the smallest inner diameter, of the specific section.

[0146] It was recognized that a bend formed according to these specifications offers particularly good guidance properties for compressed air used to clean the duct system.

[0147] For example, the curved profile of the specific section can have a radius of curvature that is at least 0.5 times, preferably at least 1 times, preferably at least 1.5 times, preferably at least 2 times, preferably at least 3 times, preferably at least 4 times, preferably at least 5 times, preferably at least 7 times, preferably at least 10 times, the inner diameter of the specific section. Optionally, the radius of curvature is at most 2 times, preferably at most 3 times, preferably at most 5 times, preferably at most 6 times, preferably at most 7 times, preferably at most 10 times, preferably at most 20 times, the inner diameter of the specific section.For example, the radius of curvature is between 0.5 and 20 times, preferably between 1.5 and 10 times, the inner diameter of the specific section.

[0148] For example, the radius of curvature is between 2 mm and 10 mm, preferably between 2.5 mm and 7 mm, preferably between 3 mm and 5 mm.

[0149] For example, this refers to the smallest or largest radius of curvature of the specific section.

[0150] Alternatively or additionally, it can also be provided that at least one end, preferably at both ends, of the specific section is adjoined by a rectilinear partial section of the channel system.

[0151] Alternatively or additionally, it can also be provided that at least one end, preferably both ends, of the specific section is or can be fluidly connected to the surroundings of the housing, in particular via an opening provided on the housing.

[0152] The specific section can be connected directly or indirectly to the housing opening. For example, the housing opening can open into the specific section. In this case, the specific section is directly connected to the housing opening. The housing opening can also open into a subsection of the duct system located between the opening and the specific section. In this case, the specific section is indirectly connected to the housing opening.

[0153] Alternatively or additionally, it can also be provided that at least one element, such as a valve, sensor and / or connecting element, is arranged within the housing and / or on the housing and at least one connecting piece of the element, in particular one which transmits fluid pressure and is permeable to a fluid and / or through which a fluid can flow, projects through at least one opening in the housing into the channel system, wherein a hose-shaped and / or plug-shaped sealing means is provided which is arranged at least partially in the region of the housing opening between the connecting piece and the housing.

[0154] The connecting piece advantageously allows the element to be arranged and / or fixed at least partially on the housing.

[0155] In one embodiment, the connecting piece can be used to establish or produce a fluid connection and / or a fluid pressure-transmitting connection between the channel system and at least parts of the element (which are located, for example, outside the housing and / or the channel system).

[0156] Because the sealant is tubular or plug-shaped, it can be particularly easily positioned between the connector and the housing. For example, the sealant can be attached to the connector either detachably or permanently.

[0157] The element and the sealant can be non-destructively removable or formed as a single piece.

[0158] A plug-shaped sealant can, for example, be a sealant constructed like a cork. The sealant can optionally be made of cork, plastic, and / or rubber.

[0159] Preferably, in the context of this application, a tubular sealant is understood to mean a sealant which has a length in the main extension direction of the sealant which is at least one time, preferably at least two times, preferably at least three times, preferably at least five times, preferably at least seven times, preferably at least ten times, preferably at least twenty times, preferably at least thirty times, preferably at least fifty times, preferably at least one hundred times, a diameter, in particular an inner or outer diameter, of the sealant.

[0160] For example, the sealant has a length in the main extension direction of the sealant of between 1 mm and 10 mm, preferably between 1 mm and 8 mm, preferably between 2 mm and 8 mm, preferably between 2 mm and 5 mm.

[0161] Alternatively or additionally, it can also be provided that the connecting piece is at least partially hollow-cylindrical, the outer diameter of the connecting piece is smaller than the diameter of the housing opening and / or at least one end section of the sealing means, preferably the sealing means along its entire length, is slipped over the connecting piece, in particular over a hollow-cylindrical part of the connecting piece.

[0162] This allows the sealant to be provided together with the element, for example, and the sealant can thus be reliably positioned when the connector is inserted into the housing opening.

[0163] Alternatively or additionally, it can also be provided that the sealing means protrudes at least partially from the duct system and / or protrudes at least partially into the duct system and / or comprises a plastic material and / or a rubber material.

[0164] This allows a particularly good seal to be achieved between the connector and the housing along an extended section, in particular along the entire length of the sealant.

[0165] The rubber material can be silicone or rubber, for example.

[0166] Alternatively or additionally, it can also be provided that at least one further channel system is formed integrally within the housing, and preferably at least one specific section of the further channel system has a curved course along a main extension of the specific section, wherein preferably the further channel system is fluidically separated from the at least one other channel system (i.e. in particular the first channel system) or can be separated, in particular by means of a valve provided or providable within the housing or on the housing.

[0167] For example, a volume with adjustable fluid pressure can be fluidly connected or connectable to each of the at least two channel systems, or such a volume can be provided.

[0168] In addition, the same advantages apply when more than one channel system is created as with the at least one channel system (the first channel system) described above.

[0169] To better distinguish it from the first canal system, the further canal system can also be referred to as a second canal system.

[0170] Preferably, in the sense of this application, the two channel systems are fluidically separated from each other if the two channel systems are at most fluidically connected to each other via the bypass of the housing.

[0171] The further channel system now described can advantageously have all the features, individually and in any combination, that were described with regard to the first channel system. In particular, the radius of curvature and / or the inner diameter of the specific section of the further channel system can assume the previously described values. Unless otherwise indicated by the context, the two channel systems can be designed completely or partially differently, for example with regard to the inner diameter and / or radius of curvature of the specific section.

[0172] Alternatively or additionally, the device according to the second aspect of the invention can also be provided with a housing according to the third aspect of the invention.

[0173] As a result, all or at least some of the components of the device can be reliably and safely provided within the housing or on the housing and / or brought into operative connection with one another.

[0174] For example, the compression device can be provided outside the housing and can be connected or connectable to the housing via a hose. As a result, the chamber of the compression device can be fluidly connected or connectable very simply and reliably to the at least one (first / second) channel system and / or the first pressure adjustment device (in particular via the at least one (first / second) channel system).

[0175] Alternatively or additionally, in the device according to the second aspect of the invention, it can also be provided that the storage volume is formed integrally within the housing.

[0176] This enables a very compact design of the device and reliable operation.

[0177] An integral design of the storage volume can be realized, for example, by a volume that is at least partially completely enclosed within a housing body. This allows for a high level of tightness. The enclosed volume can then be connected or connectable to one of the channel systems.

[0178] For example, the template volume is completely or at least partially formed by the first and / or second channel system.

[0179] Alternatively or additionally, the device according to the second aspect of the invention can also be provided such that one channel system (in particular the first or second channel system) of the at least two channel systems is fluidically connected to the supply volume or at least parts of one channel system form the supply volume and the other channel system (in particular the second or first channel system) of the at least two channel systems is fluidically connected or connectable to the chamber of the compression device.

[0180] For example, a fluid line, such as a hose, can be used to establish a connection between the chamber of the compression device and the corresponding other channel system. For this purpose, the fluid line can be connected to an opening in the housing that opens into the corresponding other channel system.

[0181] Alternatively or additionally, the device according to the second aspect of the invention can also be provided with the differential pressure sensor being arranged or being able to be arranged within the housing or on the housing in such a way that the two sides of the differential pressure sensor can be subjected to the pressures existing in the two channel systems and thus a differential pressure between the fluid pressure in the supply volume and the fluid pressure existing in the chamber of the compression device can be measured by means of the differential pressure sensor.

[0182] This enables a particularly compact device.

[0183] Thus, advantageously, one side of the differential pressure sensor is subjected to the fluid pressure in the supply volume, and the other side of the differential pressure sensor is subjected to the fluid pressure in the chamber. Alternatively or additionally, the device according to the second aspect of the invention can also be provided with (i) the compression device being provided outside the housing and / or the chamber of the compression device being fluidly connected or connectable, in particular by means of a fluid line, to at least one of the channel systems (in particular the second channel system), (ii) the first pressure adjustment device being arranged within the housing or on the housing, (iii) the second pressure adjustment device being arranged within the housing or on the housing, (iv) the differential pressure sensor being arranged within the housing or on the housing,(v) the chamber of the compression device is or can be fluidly connected to the first pressure adjustment device at least partially via at least one of the channel systems (in particular the second channel system), and / or (vi) the supply volume is formed by at least a part of at least one of the channel systems (in particular the first channel system) and / or the supply volume is or can be fluidly connected to the second pressure adjustment device, in particular at least partially via at least one of the channel systems (in particular the first channel system).

[0184] Alternatively or additionally, in the device according to the second aspect of the invention, it can also be provided that the valve element is a valve of the first pressure adjustment device and by means of the valve element a fluid connection between a pump of the first pressure adjustment device and the chamber of the compression device can be controlled, in particular opened and closed.

[0185] Alternatively or additionally, in the device according to the second aspect of the invention, it can also be provided that the valve element is a valve of the second pressure adjustment device and by means of the valve element a fluid connection between a pump of the second pressure adjustment device and the supply volume can be controlled, in particular opened and closed.

[0186] Short description of the drawings

[0187] Further features and advantages of the invention will become apparent from the following description, in which preferred embodiments of the invention are explained with reference to schematic drawings.

[0188] Showing:

[0189] Fig. 1 is a schematic representation of a device according to the second aspect of

[0190] Invention;

[0191] Fig. 2a is a diagram of a course of the first and second specific fluid pressure in a chamber and a supply volume of a compression device of the device from Fig. 1;

[0192] Fig. 2b is a diagram of a course of the fluid pressure in the chamber of the compression device of the device of Fig. 1;

[0193] Fig. 2c is a diagram of a first course of pressure changes caused by pulse waves of a living being in the chamber of the compression device of the device of Fig. 1 under first conditions;

[0194] Fig. 2d is a diagram of a second curve of pressure changes caused by pulse waves of a living being in the chamber of the compression device of the device of Fig. 1 under second conditions; Fig. 2e is a diagram of a third curve of pressure changes caused by pulse waves of a living being in the chamber of the compression device of the device of Fig. 1 under third conditions;

[0195] Fig. 2f is a diagram of a fourth course of pressure changes caused by pulse waves of a living being in the chamber of the compression device of the device of Fig. 1 under fourth conditions;

[0196] Fig. 3 is a flowchart of a method according to the first aspect of the invention;

[0197] Fig. 4a is a schematic cross-sectional view of a housing according to the third aspect of the invention;

[0198] Fig. 4b is an enlarged schematic detail view of a section of Fig. 4a; and

[0199] Fig. 5 is a schematic representation of parts of a device according to the second

[0200] Aspect of the invention in a further embodiment.

[0201] Description of the embodiments

[0202] Fig. 1 shows a schematic representation of a device 1 for non-invasive blood pressure measurement according to the second aspect of the invention.

[0203] The device 1 comprises a compression device 3 in the form of a blood pressure cuff. The compression device 3 is placed around a part 5 of the body of a living being, namely a human upper arm. The upper arm is shown schematically in a sectional view, with the cross-sectional area hatched.

[0204] With the compression device 3, a time-varying pressure can be exerted on the upper arm 5 by varying a first specific fluid pressure within a chamber 7 of the compression device 3 over time by means of a first pressure adjustment device 9 provided by the device 1. The chamber 7 circumferentially surrounds the upper arm 5 of the person, as illustrated in Fig. 1.

[0205] The first pressure adjustment device 9 is a pump with which fluid, namely air, can be pumped into the chamber 7 and with which the chamber 7 can also be emptied by pumping fluid out of the chamber 7. This allows the first specific fluid pressure within the chamber 7 to be adjusted. For this purpose, the pressure adjustment device 9 is fluidly connected to the chamber 7 via a fluid line 11.

[0206] In addition, the device 1 also has a hollow body 13 with an enclosed storage volume 15. In the present case, the hollow body 13 is a cube-shaped body, and the storage volume 15 is also cube-shaped. However, a different configuration of the hollow body and / or storage volume, such as a cylindrical or spherical shape, would also be possible.

[0207] The storage volume is connected to a second pressure adjustment device 19 via a fluid line 17. The second pressure adjustment device 19 is a pump with which fluid, namely air, can be pumped into the storage volume 15 and with which the storage volume 15 can also be emptied by pumping fluid out of it. This allows a second specific fluid pressure to be adjusted within the storage volume 15.

[0208] In the present case, the fluid pressure existing in the supply volume 15 is determined solely by the respective second specific fluid pressure, and is therefore identical to it. In contrast, the fluid pressure existing in chamber 7 is determined by the respective first specific fluid pressure, as well as by a time-dependent deformation of the cuff 3 and the associated volume change within chamber 7 due to the force influence that the pulse waves exert via the human blood vessel walls via the human upper arm 5 on the cuff 3 and thus on the chamber 7. The time-dependent deformation represents the pulse waves, which are thus measurable as pressure variations and can at least conceptually be represented as superimposed on the first specific fluid pressure.

[0209] In addition, the device 1 also includes a differential pressure sensor 21. The differential pressure sensor 21 has a first side 23, which is fluidly connected to the chamber 7 via a fluid line 25. As a result, the first side 23 of the differential pressure sensor 21 is subjected to the respective fluid pressure within the chamber 7. The differential pressure sensor 21 has a second side 27, which is fluidly connected to the supply volume 15 via a fluid line 29. As a result, the second side 27 of the differential pressure sensor 21 is subjected to the respective fluid pressure within the supply volume 15. With this circuit, the differential pressure value output by the differential pressure sensor 21 corresponds to the value of the fluid pressure within the chamber 7 minus the value of the fluid pressure within the supply volume 15 (or generally "fluid pressure on the first side minus fluid pressure on the second side").

[0210] By means of the first pressure adjustment device 9, a first specific fluid pressure can be adjusted within the chamber 7 when the device 1 is used, as described above. And by means of the second pressure adjustment device 19, a second specific fluid pressure can be adjusted within the supply volume 15 when the device 1 is used, as described above.

[0211] Fig. 2a shows a diagram of an exemplary course of the first specific fluid pressure P controlled by the first pressure adjustment device 9 s in the chamber 7 of the compression device 3 of the device 1 and an exemplary course of the second specific fluid pressure Pv in the supply volume 15, controlled by the second pressure adjustment device 19.

[0212] For example, the first specific fluid pressure Ps can be continuously changed, in particular reduced, from a first initial pressure value Psi at time t1 at a constant rate of change (in mmHg per second) to a first target pressure value Ps2 at time t2. For example, the measurement period (t1-t2) is 60 seconds. Accordingly, during the same period (t1-t2), the second specific fluid pressure Pv in the supply volume 15 can be changed from a second initial pressure value P Vi The first specific fluid pressure Ps is continuously changed, in particular reduced, to a second target pressure value Pv2 at the same rate of change as before. At all times, there is an identical pressure difference of APsv between the first specific fluid pressure in the chamber 7 and the second specific fluid pressure in the supply volume 15.

[0213] However, the actual fluid pressure PK measurable within chamber 7 (relative to atmosphere) during the period t1 to t2 is influenced, in addition to the first specific fluid pressure Ps, at least by the subject's pulse waves, which propagate from the heart through the subject's blood vessel walls, as already noted above. The pulse waves exert a variable force on cuff 3, thus changing the volume of chamber 7 and thus the fluid pressure within chamber 7 in a time-dependent manner.

[0214] Fig. 2b shows a diagram of an exemplary and highly schematically illustrated course of the fluid pressure PK in the chamber 7 of the compression device 3 of the device 1 during the period t1 to t2. The course of the fluid pressure during the period t1 to t2 in Fig. 2b can thus be conceptually imagined as an additive composition of the course of the first specific fluid pressure (Fig. 2a) and the course of the pressure changes due to the pulse waves. In other words, the pressure changes due to the pulse waves are imposed on the course of the first specific fluid pressure (Fig. 2a). In fact, conversely, the course of the first specific fluid pressure Ps shown in Fig. 2a can also be derived from the course of the actual fluid pressure in Fig. 2b as a "falling baseline" of the pulse waves.

[0215] However, if during the period t1 to t2 the fluid pressure in chamber 7 is not measured against atmosphere, the course of which is shown in Fig. 2b, but rather against the fluid pressure within the supply volume 15 as the supply pressure, i.e. if the differential pressure APKV is measured, the continuous change in the supply pressure also plays a role in the analysis. Since in this case there is always a constant pressure difference of APsv between the first and second specific fluid pressures (Fig. 2a), the course of the differential pressure APKV corresponds precisely to the course of the pulse waves (or the pressure fluctuations caused by them) on a horizontally extending "baseline", as schematically illustrated in Fig. 2c.

[0216] As can be seen in Fig. 2c, the baseline (shown as a dot-dash line) runs at a pressure value of PG. The value of PG corresponds in particular to the pressure difference APsv between the first and second specific fluid pressures (Fig. 2a), i.e., PG = APSV-

[0217] By selecting the pressure difference APsv, the position of the "baseline" can be shifted. If the second specific fluid pressure is increased and thus the pressure difference APsv is reduced, the curve from Fig. 2c is shifted downwards. If the first and second specific fluid pressures are identical (and thus the pressure difference is zero), the baseline coincides exactly with the time axis (t) of the diagram, as shown in Fig. 2d. If the second specific fluid pressure is increased even further, the "baseline" shifts further downwards and with it the course of the pulse waves, as shown in Fig. 2e. For comparison, the course of the pulse waves from Fig. 2c is shown in dashed lines in Figs. 2d and 2e.

[0218] These illustrations clearly show how, by adjusting the second specific fluid pressure, the range of values ​​P M in to P Max of the pressure fluctuations caused by the pulse waves, and how the measuring range of a differential pressure sensor can be used to advantage. For example, the value range can be adjusted with P M > 0, so that an A / D converter connected downstream of the differential pressure sensor or provided by it and operating only in the positive value range is optimally controlled. Alternatively, the value range can be aligned approximately symmetrically around the zero line (i.e., around the time axis) so that an A / D converter connected downstream of the differential pressure sensor or provided by it and operating in the positive and negative value ranges is optimally controlled.

[0219] Returning to the situation described in relation to Fig. 2c, however, if lines 25 and 29 are not connected to the first and second sides 23, 27, but rather interchanged with the second and first sides 27, 23 of the differential pressure sensor 21, a pulse wave pressure fluctuation curve as shown in Fig. 2f is obtained. This corresponds exactly to the curve in the diagram of Fig. 2c, but mirrored across a horizontal line.

[0220] The following table provides an overview of exemplary parameters of the individual values ​​for a non-invasive blood pressure measurement in various living beings.

[0221] Fig. 3 shows a flowchart 100 of a method for non-invasive blood pressure measurement according to the first aspect of the invention.

[0222] In particular with regard to the above detailed explanations of the device 1, the method advantageously comprises the following.

[0223] In 101, a time-varying pressure is exerted on at least the part 5 of the body of a living being by means of the compression device 3 during a measuring period (from ti to tz), in that the first specific fluid pressure within the chamber 7 of the compression device 3 is changed in a time-dependent manner during the measuring period by means of the first pressure adjustment device 9 (for example from a first initial pressure value to a first target pressure value).

[0224] In 103, at different measuring times during the measuring period, at which different first specific fluid pressures are set, at least one measured value of the differential pressure existing at the respective measuring time between the (current) fluid pressure within the chamber 7 and the (current) fluid pressure within the supply volume 15 is recorded.

[0225] In this case, the second specific fluid pressure within the supply volume 15 is adjusted by means of the second pressure adjustment device 19 in such a way that at least at each measuring time point the fluid pressure within the supply volume 15 is different from at least the first specific fluid pressure set at the respective measuring time point, namely on the one hand it is smaller and on the other hand it has a constant difference of 25 mmHg (for example from a second initial pressure value to a second target pressure value).

[0226] The recorded measured values ​​describe a measurement curve which represents and / or depicts and / or makes it possible to determine the course of the pulse waves of the blood pressure of the living being.

[0227] In 105, the recorded measured values ​​are evaluated and parameters of the human blood pressure, such as the systolic blood pressure and / or the diastolic blood pressure, are determined based on at least one result of the evaluation.

[0228] Fig. 4a shows a schematic cross-sectional view of a housing 31 according to the third aspect of the invention.

[0229] A channel system 33 (which can be referred to in particular as the first channel system) is integrally formed within the housing 31. For this purpose, the channel system 33 is formed within a solid housing body 35. This is particularly simple and reliable because the housing 31 is manufactured entirely by 3D printing, and thus internal (hollow) structures can also be formed in almost any desired shape. The channel system 33 has a specific section 37 that has a curved profile along a main extension of the specific section 37. The curved profile of the specific section 37 has a radius of curvature RK that is larger than an inner diameter of the specific section 37.

[0230] A linear sub-section 39 of the channel system 33 adjoins each end of the specific section 37. Furthermore, the two ends of the specific section 37 are each fluidly connected or connectable to the surroundings of the housing 31 via linear sections 39 and via openings 41 provided on the housing 31.

[0231] Within the housing 31, a further channel system 43 (which can in particular be referred to as a second channel system) is integrally formed. The further channel system 43 also has a specific section 45, which has a curved course along a main extent of the specific section 45. Furthermore, the two ends of the specific section 45 are each fluidically connected or connectable to the surroundings of the housing 31 via straight sections 47 and via openings 49 provided on the housing 31. The channel system 43 is fluidically separated from the other channel system 33. This means that the two channel systems 33, 43 are fluidically connected or connectable to one another only via the surroundings of the housing 31.

[0232] Thanks to the curved profiles of the specific sections 37, 45, the channel systems 33, 43 can be easily and reliably freed of support material after 3D printing by applying compressed air to the channel systems 33, 43 via openings 41 and 49, thus flushing them. The curved profiles of the specific sections 37, 45 guide the compressed air effectively.

[0233] A sensor element in the form of a differential pressure sensor 51 is arranged on the housing 31, although this need not be provided in other embodiments. Fig. 4b shows an enlarged schematic detail of a section framed by dashed lines in Fig. 4a. Some features of the differential pressure sensor 51 and the adjacent structures of the housing 31 can be seen in the detail of Fig. 4b.

[0234] The differential pressure sensor 51 has two hollow-cylindrical connecting pieces 53a, 53b that are permeable to a fluid and through which a fluid can flow (and, above all, transmit fluid pressure). The first connecting piece 53a projects through the housing opening 41 into the linear section 39 and thus into the channel system 33. The second connecting piece 53b projects through the housing opening 49 into the linear section 47 and thus into the channel system 43. This allows both sides of the differential pressure sensor 51 to be subjected to the pressures existing in the two channel systems 33, 43, and the differential pressure between these channel systems 33, 43 can thus be determined.

[0235] A tubular sealant 55a, 55b is placed over each of the connecting pieces 53a, 53b. When the differential pressure sensor 51 is in the installed state, the respective sealant 55a, 55b is arranged at least partially in the area of ​​the respective housing opening 41, 49 between the respective connecting piece 53a, 53b and the housing 31. The sealant 55a, 55b protrudes at least partially from the respective channel system 33, 43 and also protrudes at least partially into the respective channel system 33, 43.

[0236] By means of the sealing means 55a, 55b, a sealing of the channel systems 33, 43 against the environment of the housing 31 can be achieved particularly advantageously despite manufacturing tolerances (particularly of the housing 31 in 3D printing manufacturing processes). The housing 31 can be used as a housing for a device for non-invasive blood pressure measurement. For example, this could be a device for non-invasive blood pressure measurement according to the second aspect of the invention, such as the device 1 described above.

[0237] Fig. 5 shows a schematic representation of individual components of a device 57 according to the second aspect of the invention in a further embodiment. The device 57 includes, among other things, a housing 31. The housing 31 can be designed similarly or identically to the housing 31 described with reference to Fig. 4a, which is why the housing and its parts are provided with the same reference numerals in Fig. 5 as in Fig. 4a.

[0238] In the device 57, a storage volume 59 is formed integrally within the housing 31, specifically by the channel system 43. The channel system 33 is connected or connectable via a fluid line 61 to a chamber of the compression device provided outside the housing 31 (neither is shown in Fig. 5). The fluid line 61 can be connectable to the housing 31 (for example, by means of a connecting element having a connecting piece), wherein a sealing means, which can be designed in a similar manner to the sealing means 55a, 55b described with reference to Fig. 4b, can also be provided.

[0239] By means of the differential pressure sensor 51, a differential pressure between the fluid pressure in the supply volume 59 and the fluid pressure in the chamber of the compression device can be measured.

[0240] A first pressure adjustment device is arranged on the housing 31, which, however, is not located in the sectional plane of Fig. 5 and is therefore not shown in Fig. 5. The first pressure adjustment device is fluidly connected to the channel system 33 via a part of the channel system 33 running perpendicular to the plane of the drawing in Fig. 5. By means of the first pressure adjustment device, the fluid pressure within the chamber of the compression device, which is fluidly connected to the channel system 33 via the fluid line 61, can be adjusted. In addition, a second pressure adjustment device 63 is arranged on the housing 31, with which the fluid pressure within the channel system 43 and thus within the supply volume 59 can be adjusted.

[0241] The second pressure adjustment device 63 can be connectable to the housing 31 (for example by means of a connecting element having a connecting piece), wherein a sealing means can also be provided, which can be designed in a similar manner to the sealing means 55a, 55b described with reference to Fig. 4b.

[0242] Further components of the device 57 can advantageously be arranged on the housing 31 or within the housing 31, even if these are not described in more detail here.

[0243] A housing according to the third aspect of the invention (such as housing 31) can thus advantageously provide structures of channel systems for fluidically connecting different components of a device for non-invasive blood pressure measurement (e.g., according to the third aspect of the invention, such as device 57). The integral design of the channel systems, for example, can prevent or at least reduce pressure losses. Furthermore, the risk of incorrectly wiring the components due to the predefined channel systems can be avoided or at least reduced.

[0244] For example, in the device 1 described with reference to Fig. 1, the fluid lines 11, 17, 25, 29 could each be formed entirely or partially as a channel system within a housing according to the third aspect of the invention. The features disclosed in the preceding description, in the drawings, and in the claims can be essential to the invention in its various embodiments, both individually and in any combination.

[0245] List of reference symbols

[0246] 1 device

[0247] 3 Compression device

[0248] 5 Part of the body of a living being

[0249] 7th chamber

[0250] 9 First pressure adjustment device

[0251] 11 Fluid line

[0252] 13 hollow bodies

[0253] 15 template volumes

[0254] 17 Fluid line

[0255] 19 Second pressure adjustment device

[0256] 21 Differential pressure sensor

[0257] 23 First page of the differential pressure sensor

[0258] 25 Fluid line

[0259] TI Second side of the differential pressure sensor

[0260] 29 Fluid line

[0261] 31 housings

[0262] 33 Canal system

[0263] 35 housing body

[0264] 37 Specific Section

[0265] 39 Straight section

[0266] 41 Opening

[0267] 43 Canal system

[0268] 45 Specific Section

[0269] 47 Part-Section

[0270] 49 Opening

[0271] 51 Differential pressure sensor

[0272] 53a, 53b connecting piece

[0273] 55a, 55b Sealant

[0274] 57 Device

[0275] 59 Supply volume 61 Fluid line

[0276] 63 Pressure adjustment device

[0277] 100 Flowchart

[0278] 101 Applying a time-varying pressure to a body part of a living being

[0279] 103 Recording measured values ​​of a differential pressure

[0280] 105 Evaluation of the measured values ​​and determination of parameters of the blood pressure of the living being

[0281] PG fluid pressure

[0282] PK fluid pressure

[0283] PlVlax fluid pressure

[0284] Pft / Iin fluid pressure

[0285] Ps First specific fluid pressure

[0286] Psi First specific fluid pressure

[0287] Ps2 First specific fluid pressure

[0288] Pv Second specific fluid pressure

[0289] Pvi Second specific fluid pressure

[0290] Pv2 Second specific fluid pressure

[0291] APsv pressure difference

[0292] ÄPKV differential pressure

[0293] RK radius of curvature t time axis tl, t2 time

Claims

Patent claims Method for non-invasive blood pressure measurement, comprising exerting a time-varying pressure on at least part of the body of a living being by means of a compression device at least during a measuring period, in that a first specific fluid pressure within a chamber of the compression device is changed in a time-dependent manner at least during the measuring period by means of a first pressure adjustment device, wherein at different measuring times during the measuring period, at which at least partially different first specific fluid pressures are set, at least one measured value of a differential pressure existing at the respective measuring time between the fluid pressure within the chamber and the fluid pressure within a supply volume is recorded, and wherein a second specific fluid pressure within the supply volume is adjusted by means of a second pressure adjustment device.Method according to claim 1, wherein the second specific fluid pressure within the supply volume is adjusted at least during the measurement period and / or time-dependently by means of the second pressure adjustment device. Method according to one of the preceding claims, wherein the second specific fluid pressure within the supply volume is adjusted by means of the second pressure adjustment device such that at least at one, preferably at each, measurement time, the fluid pressure within the supply volume is different from at least the first specific fluid pressure set at the respective measurement time and / or the fluid pressure existing in the chamber at the respective measurement time.Method according to one of the preceding claims, wherein the first specific fluid pressure within the chamber is set, in particular by means of the first pressure adjustment device and / or before the measuring period, to a first initial pressure value, which is preferably above the systolic blood pressure of the living being, and preferably the first specific fluid pressure is changed from the first initial pressure value, in particular at least during the measuring period, in a time-dependent manner, preferably until a first target pressure value, which is preferably below the diastolic blood pressure of the living being, is reached. Method according to one of the preceding claims, wherein the first specific fluid pressure is changed continuously or stepwise, in particular at least during the measuring period, by means of the first pressure adjustment device.Method according to one of the preceding claims, wherein the second specific fluid pressure within the supply volume is set to a second initial pressure value, in particular by means of the second pressure adjustment device and / or before the measuring period, and / or, in particular starting from the second initial pressure value and / or at least during the measuring period, is changed in a time-dependent manner, preferably until a second target pressure value is reached. Method according to one of the preceding claims, wherein the second specific fluid pressure, in particular at least during the measuring period, within the supply volume (i) is adjusted such that the ratio of the first specific fluid pressure in the chamber and the second specific fluid flow within the supply volume, in particular at each measurement time, has a value (a) of between 0.5 and less than 1.0, in particular of between 0.6 and less than 1.0, in particular of between 0.7 and less than 1.0, in particular of between 0.9 and less than 1.0, and / or (b) of between more than 1.0 and 1.5, in particular of between more than 1.0 and 1.4, in particular of between more than 1.0 and 1.3, in particular of between more than 1.0 and 1.1, (ii) is changed at least temporarily simultaneously with the first specific fluid pressure within the chamber, (iii) is changed in phase with the first specific fluid pressure within the chamber, (iv) has a pressure difference in magnitude to the first specific fluid pressure within the chamber of at least one, preferably at least two, preferably at least three, preferably at least four, preferably at least five times the maximum pressure change caused by the pulse waves during the measurement period, and / or (v) is changed at an identical rate of change as the first specific fluid pressure within the chamber. Method according to one of the preceding claims, wherein, in particular at least at the individual measuring times, the pressure difference between the first specific fluid pressure within the chamber and the second specific fluid pressure within the supply volume is set (i) to a constant value and / or (ii) to a value of (a) 1 mmHg or more than 1 mmHg, (b) 600 mmHg or less than 600 mmHg and / or (c) between 1 mmHg and 600, preferably between 1 mmHg and 100 mmHg, preferably between 10 mmHg and 50 mmHg, such as 1 mmHg, 10 mmHg, 25 mmHg, 30 mmHg or 50 mmHg.Method according to one of the preceding claims, wherein the, in particular current, fluid pressure within the supply volume is not influenced by the living being or parts thereof, in particular not by the blood pressure of the living being and / or by pulse waves propagating via the blood vessels of the living being. Method according to one of the preceding claims, wherein the first specific fluid pressure in the chamber and the second specific fluid pressure in the supply volume are controlled and / or adjusted, in particular at least during the measurement period and / or at least for each measurement, such that, in particular at least during the measurement period and / or at least for each measurement, the first specific fluid pressure, preferably at any time, is at a greater or lesser value than the second specific fluid pressure. Method according to one of the preceding claims, wherein the recorded measured values ​​describe a measurement curve which represents and / or depicts and / or makes ascertainable a course of the pulse waves of the blood pressure of the living being. Method according to one of the preceding claims, wherein the differential pressure between the, in particular current, fluid pressure in the chamber and the, in particular current, fluid pressure in the supply volume is measured by means of a differential pressure sensor, wherein preferably a first side of the differential pressure sensor is fluidically connected to the chamber and a second side of the differential pressure sensor is fluidically connected to the supply volume, and in particular the differential pressure sensor delivers positive pressure values ​​when the, in particular current, fluid pressure in the chamber is greater than the, in particular current, fluid pressure in the supply volume, and the differential pressure sensor delivers negative pressure values ​​when the, in particular current,The fluid pressure in the chamber is lower than the, in particular current, fluid pressure in the supply volume. Method according to one of the preceding claims, wherein the compression device comprises or represents a blood pressure measuring cuff, wherein the part of the body of the living being can preferably be compressed to varying degrees by the cuff, and / or wherein the chamber is a chamber of the cuff, in particular one that can be filled and emptied with a fluid. A device for non-invasive blood pressure measurement, comprising a compression device, by means of which a time-varying pressure can be exerted on at least a part of the body of a living being, at least during a measurement period, in that a first specific fluid pressure within a chamber of the compression device can be changed in a time-dependent manner, at least during the measurement period, by means of a first pressure adjustment device provided by the device.wherein the device comprises a differential pressure sensor and an object with an enclosed supply volume, and the device is configured to record at least one measured value of a differential pressure existing at the respective measuring time between the fluid pressure within the chamber and the fluid pressure within the supply volume with the differential pressure sensor at different measuring times during the measuring period, at which at least partially different first specific fluid pressures are set, and wherein the device is configured to adjust a second specific fluid pressure within the supply volume by means of a second pressure adjustment device provided by the device. Housing, in particular for a device for non-invasive blood pressure measurement, such as a device according to claim 14, wherein at least one channel system is integrally formed within the housing, characterized in thatthat at least one specific section of the channel system has a curved course along a main extension of the specific section., Housing according to claim 15, wherein the channel system is at least partially formed, in particular at least the specific section, within a solid housing body. Housing according to one of claims 15 to 16, wherein the housing, the channel system, in particular the specific section, and / or the housing body is at least partially produced by 3D printing. Housing according to one of claims 15 to 17, wherein the curved course of the specific section has a radius of curvature that is greater than or equal to half an inner diameter, in particular half the smallest inner diameter, of the specific section. Housing according to one of claims 15 to 18, wherein a rectilinear partial section of the channel system adjoins at least one end, preferably both ends, of the specific section.Housing according to one of claims 15 to 19, wherein at least one end, preferably both ends, of the specific section is or can be fluidly connected to the surroundings of the housing, in particular via an opening provided on the housing. Housing according to one of claims 15 to 20 or according to the preamble of claim 15, wherein at least one element, such as a valve, sensor and / or connecting element, is arranged within the housing and / or on the housing and at least one connecting piece of the element, in particular one which transmits fluid pressure and is permeable to a fluid and / or through which a fluid can flow, projects through at least one opening in the housing into the channel system, wherein a tubular and / or plug-shaped sealing means is provided which is arranged at least partially in the region of the housing opening between the connecting piece and the housing.Housing according to claim 21, wherein the connecting piece is at least partially hollow-cylindrical, the outer diameter of the connecting piece is smaller than the diameter of the housing opening, and / or at least one end portion of the sealing means, preferably the sealing means along its entire length, is slipped over the connecting piece, in particular over a hollow-cylindrical part of the connecting piece. Housing according to one of claims 21 to 22, wherein the sealing means protrudes at least partially from the channel system and / or protrudes at least partially into the channel system and / or comprises a plastic material and / or a rubber material.Housing according to one of the preceding claims 15 to 23, wherein at least one further channel system is formed integrally within the housing, and preferably at least one specific section of the further channel system has a curved course along a main extension of the specific section, wherein preferably the further channel system is fluidically separated from the at least one other channel system or can be separated, in particular by means of a valve provided or providable within the housing or on the housing. The device according to claim 14, comprising a housing according to any one of the preceding claims 15 to 24. The device according to claim 25, wherein the storage volume is integrally formed within the housing. The device according to any one of claims 25 to 26 together with claim 24, wherein one channel system of the at least two channel systems is fluidly connected to the storage volume or at least parts of the one channel system form the storage volume, and the other channel system of the at least two channel systems is fluidly connected or connectable to the chamber of the compression device.The device according to claim 27, wherein the differential pressure sensor is arranged or can be arranged within the housing or on the housing such that the two sides of the differential pressure sensor can be subjected to the pressures existing in the two channel systems, and thereby a differential pressure between the fluid pressure in the supply volume and the fluid pressure in the chamber of the compression device can be measured by means of the differential pressure sensor. The device according to one of claims 25 to 28, wherein. (i) the compression device is provided outside the housing and / or the chamber of the compression device is or can be fluidly connected to at least one of the channel systems, in particular by means of a fluid line, (ii) the first pressure adjustment device is arranged within the housing or on the housing, (iii) the second pressure adjustment device is arranged within the housing or on the housing, (iv) the differential pressure sensor is arranged inside the housing or on the housing, (v) the chamber of the compression device is at least partially fluidly connected or connectable to the first pressure adjustment device via at least one of the channel systems, and / or (vi) the supply volume is formed by at least a portion of at least one of the channel systems and / or the supply volume is or can be fluidly connected to the second pressure adjustment device, in particular at least partially via at least one of the channel systems. Device according to one of claims 25 to 29 together with claim 21, wherein the valve element is a valve of the first pressure adjustment device, and a fluid connection between a pump of the first pressure adjustment device and the chamber of the compression device can be controlled, in particular opened and closed, by means of the valve element. Device according to one of claims 25 to 29 together with claim 21, wherein the valve element is a valve of the second pressure adjustment device and by means of the valve element a fluid connection between a pump of the second pressure adjustment device and the supply volume can be controlled, in particular opened and closed.

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