Method, testing device, computer program and computer-readable storage medium for measuring blood pressure in animals

Abstract

The present invention relates to a method for medical examination of animals, in particular for blood pressure measurement. The animals are preferably legged, in particular felines. In this method, a curve containing information about the animal's arterial blood flow, in particular a photoplethysmogram, is recorded. According to the invention, the curve is divided into a plurality of curve sections, each curve section corresponding to a heartbeat. According to another independent aspect, a sensor or a subset of sensors is selected from a plurality of sensors of the same type to perform the study.

Description

[Technical field]

[0001] The invention relates to a method for medical examination of animals according to the preamble of claim 1 or 17, as well as to an examination device, a computer program and a computer-readable storage medium.

[0002] In general, the object of the present invention is to enable or simplify non-invasive blood pressure measurement in pets, such as cats or dogs. In humans, non-invasive blood pressure measurement often involves the use of an inflatable cuff worn around the arm. However, measuring blood pressure using a cuff is not without problems for dogs, and especially for cats, because these animals are not accustomed to such tests and it can be difficult for them to wear the cuff, especially for cats. On the other hand, wearing the cuff is stressful for the animal, which can lead to erroneous measurements and is therefore something that should be avoided if possible.

[0003] However, the invention is not limited to application to pets such as cats or dogs, but can in principle also be used for any kind of animal, in particular humans.Furthermore, the invention is not limited to blood pressure measurements, but is generally designed or adapted for medical tests, in particular optical, non-invasive and / or transcutaneous tests, particularly preferably photoplethysmography and / or pulse oximetry.

[0004] In addition to cuff-based blood pressure measurements, other methods of measuring blood pressure non-invasively are already known in the prior art.

[0005] WO85 / 03211A1 relates to a method for measuring arterial blood pressure, in which the heart rate is measured by an electrocardiograph and the arterial blood flow is measured by photoplethysmography. The blood pressure is then determined from the time interval between the heart rate and the arterial pulse wave caused thereby and measured by photoplethysmography. This is done by exploiting the fact that the blood pressure is correlated to the time span between the heart rate and the arterial pulse wave caused thereby.

[0006] The time between the heart beat and the resulting arterial pulse wave is also called the pulse wave transit time.

[0007] WO89 / 08424A1 relates to a method for continuously measuring the blood pressure of a human being. The pulse transit time is continuously measured with the aid of a probe-specific calibration curve showing the pulse transit time as a function of the blood pressure volume used to determine one of the three blood pressure volumes (systolic, diastolic, mean blood pressure). To measure the pulse transit time, two electrodes are placed over the patient's heart, a sensor is attached to the ear lobe with an ear clip and an ECG is recorded. A small light source of the sensor shines through the ear lobe and the transmittance of the ear lobe, which varies proportionally to the blood pressure, is measured by a photodiode. The temporal transmittance curve shows the arrival of the pulse wave at the ear lobe relative to the systole registered by the ECG signal. The pulse transit time is thus determined relative to the distance between the heart and the ear lobe. [Prior art documents] [Patent documents]

[0008] [Patent Document 1] International Publication No. 85 / 03211A1 [Patent Document 2] International Publication No. 89 / 08424A1 Summary of the Invention [Problem to be solved by the invention]

[0009] The object of the present invention is to provide a solution which allows reliable, accurate, fast and / or non-invasive medical testing of animals such as dogs or cats, in particular blood pressure measurement, in particular without the use of a cuff, and which makes the test or measurement as comfortable as possible for the animal.

[0010] The above object is solved by a method according to claim 1 or 17, an examination device according to claim 31 or 35, a computer program according to claim 36 or a computer-readable storage medium according to claim 37. Further advantageous developments are the subject matter of the dependent claims.

[0011] The invention relates in particular to a method for the medical examination of an animal, in particular in which the blood pressure of the animal is determined. The determined blood pressure may in particular be the diastolic blood pressure.

[0012] Furthermore, the method is preferably configured and / or suitable for testing animals having legs, preferably animals from the superfamily Felidae (cat-like) or superfamily Caninoidea (dog-like), in particular animals from the family Felidae (cats) or family Caninoidea (dogs), particularly preferably animals from the subfamily Felinae (small cats) or subfamily Caninae (true dogs), in this family in particular animals from the family Canidae (wolf-like and jackal-like), particularly preferably domestic cats or domestic dogs.

[0013] In principle, however, the method is suitable for medical examinations, in particular blood pressure measurements, in any animal, but especially in humans.

[0014] In the method according to the invention, the arterial blood flow of an animal is optically examined, preferably by means of a sensor device. Particularly preferably, photoplethysmography is performed. This makes it possible to avoid the application of a cuff. Furthermore, the sensor device allows the animal to move freely during the examination, which allows for a comfortable and therefore stress-free examination for the animal. As a result, accurate and reliable examinations, in particular blood pressure measurements, can be performed.

[0015] Furthermore, the method comprises recording a curve, in particular a photoplethysmogram, containing information about the arterial blood flow of the animal, and cutting the curve into a number of curve sections, each curve section corresponding to a heart beat, in particular to a single and / or exactly one heart beat, thereby allowing reliable and accurate tests, in particular blood pressure measurements, to be performed.

[0016] The evaluation of the curve is preferably based on a number of curve sections and averaging is performed, which simplifies and / or improves the accuracy of the evaluation, in particular noise in the signal and / or in the curve sections can be suppressed and / or filtered and movement artifacts can be corrected.

[0017] It is preferred to select a subset of the curve sections for evaluation, in particular the curve sections that are not selected can be discarded, which improves the accuracy and / or reliability of the method, in particular when the test conditions lead to temporary disturbances, for example when the tested animal moves.

[0018] Preferably, a resampling method, in particular the bootstrap method, is used for the evaluation, whereby subsamples, in particular bootstrap samples, are generated from the curve sections, which contributes to the reliability and accuracy of the method.

[0019] The subsample preferably has less than 200, preferably less than 100, in particular less than 60 and / or more than 15, preferably more than 30, particularly preferably about 45 curve sections. In the present examples it is shown in a surprising manner that even such a small number of curve sections leads to reliable and accurate results with a relatively low amount of calculations.

[0020] Further preferably, less than 1000, preferably less than 500, particularly preferably less than 250, particularly preferably less than 100, very particularly preferably less than 75 and / or more than 10, preferably more than 30, particularly preferably about 50 subsamples are generated. It has been shown in a surprising manner that even with such a small number of subsamples reliable and accurate results are obtained.

[0021] From the curve sections and / or sub-samples preferably curve features are determined. Preferably a curve feature is determined for each sub-sample and / or an average value is determined from a number of curve features, preferably of the same type. This increases accuracy and reliability in determining the curve features.

[0022] Preferably, the degree of dispersion of the curve characteristics, in particular the interquartile range and / or standard deviation, is determined. Here, it is particularly preferred that multiple curves are recorded simultaneously and / or successively and one of the curves is selected for further evaluation based on the degree of dispersion. This increases the reliability and accuracy of the curve characteristics and / or blood pressure measurements.

[0023] Particularly preferably, blood pressure is measured based on the curve characteristics, preferably by means of an empirically determined correlation function.

[0024] Preferably, a heart rate curve, in particular an electrocardiogram, is recorded simultaneously with the curve, and preferably information from the heart rate curve is used to cut the curve into curve sections, the heart rate curve facilitating the division of the curve into sections corresponding to the heart beats.

[0025] Particularly preferably, the QRS complexes of the heartbeat curve or the electrocardiogram, in particular the R peaks of the QRS complexes, are used to determine the time of the heartbeat, preferably the curve is cut into curve sections at times determined by the QRS complexes, which results in an easy and accurate determination of the curve characteristics.

[0026] The heart rate curve is preferably automatically checked for usefulness. In particular, if the heart rate curve is not useful, the heart rate curve and preferably the heart rate curve and / or the curve containing information on the arterial blood flow corresponding to the respective time segment are discarded. Preferably, a new or different heart rate curve is then recorded or another time segment of the heart rate curve is used. Also preferably, a new curve is recorded and / or another time segment of the curve corresponding to another time segment of the heart rate curve is used. As a result, the usefulness of the heart rate curve is preferably a prerequisite for using the curve containing information on the arterial blood flow for further evaluation. This increases the reliability and accuracy of the method.

[0027] Preferably, the curves containing information about the arterial blood flow are automatically checked for usefulness, and if the curve is not useful, it is discarded and a new curve is recorded, which makes the method reliable and accurate.

[0028] Preferably, multiple curves are recorded simultaneously and / or consecutively and curve sections from different or multiple recorded curves are used for evaluation, which results in increased reliability and accuracy of the method.

[0029] In the method, preferably with the aid of a sensor device, the arterial blood flow of the animal is optically examined, in particular photoplethysmography, which makes the examination stress-free and comfortable for the animal, without the need for a cuff, which results in accurate and reliable examinations, in particular blood pressure measurements.

[0030] The sensor device preferably comprises one or more emitters of the same type for emitting electromagnetic radiation and a plurality of detectors of the same type for detecting the radiation emitted by the emitters, in particular the emitters and detectors form a plurality of sensors of the same type.

[0031] Preferably, a sensor or a subset of sensors is selected, which results in accurate and reliable testing, in particular blood pressure measurements, and preferably reduces the effort involved in measuring and / or evaluating the signals.

[0032] Preferably, the sensors each have a sensor area or a detection area, the sensor areas of the sensors each being at a different position and together forming a recording / sensing area, with each sensor recording / sensing or being able to record / sensing different sub-areas of the sensing area. In the case of medical tests, in particular blood pressure measurements, a certain part of the sensing area is selected. In particular, this makes it possible to dispense with very precise positioning and / or fixation of the leg relative to the sensor and / or sensor device. Thus, a very comfortable and stress-free test for the animal is possible. This results in reliable and precise tests, in particular blood pressure measurements, and preferably reduces the effort involved in measuring and / or evaluating the signals.

[0033] Preferably, it is checked whether the leg is located on the sensor or on the detection area of ​​the sensor. For this check, the signal recorded by the sensor is analyzed. In particular, it is examined whether the absolute signal strength of the signal exceeds or falls below a threshold value. In particular, this makes it possible to dispense with very precise positioning and / or fixation of the leg relative to the sensor and / or sensor device. Thus, a very comfortable and stress-free examination for the animal is possible. This results in an efficient, fast, accurate and reliable examination, in particular blood pressure measurement.

[0034] Preferably, the sensor is used to record several curves or one curve at a time, containing information about the arterial blood flow, in particular the photoplethysmogram. At least one of the curves or parts thereof can be selected for evaluation. In particular, (only) a subset of all recorded curves or parts thereof is selected for evaluation and / or curves or parts thereof that are not selected are discarded. In particular, this allows to correct movement artefacts or errors caused by movements of the animal and / or legs during the measurement and / or recording. This results in accurate and reliable tests, in particular blood pressure measurements.

[0035] Particularly preferably, the quality of the recorded curve is determined by statistical analysis, and the curve with the highest quality is selected for evaluation. In principle, a plurality of curves of the same or similar quality can be selected. In particular, this can compensate for movement artifacts or errors caused by the movement of the animal and / or leg during measurement and / or recording. This results in a highly reliable and accurate examination, particularly blood pressure measurement.

[0036] The curve selected for evaluation is preferably divided into curve sections, and particularly preferably, only a subset of the curve sections of the selected curve is used for evaluation. In particular, this can compensate for movement artifacts or errors caused by the movement of the animal and / or leg during measurement and / or recording. This results in an accurate and reliable examination, particularly blood pressure measurement.

[0037] Preferably, a plurality of curves, particularly curves are recorded in sequence, the curves are divided into curve sections, and the curve sections of the curves recorded in sequence with the same sensor are used for evaluation. This results in a highly reliable and accurate examination, particularly blood pressure measurement. In particular, this method can be applied even when the animal moves during the examination and individual curves or curve sections become unusable.

[0038] Alternatively or additionally, a plurality of curves can be recorded simultaneously, the curves can be divided into curve sections, and the curve sections of the curves recorded simultaneously with different sensors are used for evaluation. This results in a highly reliable and accurate examination, particularly blood pressure measurement. In particular, this method can be applied even when the animal moves during the examination and individual curves or curve sections become unavailable.

[0039] The proposed method is particularly flexible since several curves can be recorded simultaneously and / or successively and curve sections of one or more of these curves can be used for the evaluation. The curves recorded simultaneously with different sensors preferably represent different regions of the cat's leg, since they are recorded in particular at different positions. This allows reliable and accurate testing, especially blood pressure measurements, to be performed even if the leg is not in an optimal position relative to one or more of the sensors and / or if the leg moves during the test.

[0040] Preferably, the curve characteristics, in particular the pulse transit time, are determined by the curve. From the curve characteristics, in particular the pulse transit time, the blood pressure is determined by means of a correlation function, preferably empirically determined.

[0041] The curve is preferably cut into curve sections, each of which corresponds in particular exactly to one heartbeat. From these curve sections, an average value is preferably calculated. In particular, this allows to correct movement artifacts or errors caused by movements of the animal and / or legs during the measurement and / or recording. This results in reliable and accurate tests, in particular blood pressure measurements.

[0042] In particular, it is preferred to record the heart rate curve simultaneously with the curve and to use the heart rate information from the heart rate to cut the curve into sections, which results in reliable and accurate testing, especially blood pressure measurements.

[0043] According to another aspect, the invention relates to an examination device for medical examination, in particular blood pressure measurement, of animals, in particular of legged animals, particularly preferably of felines.

[0044] The examination apparatus comprises a sensor device for performing an optical examination, in particular photoplethysmography, of the arterial blood flow of an animal.

[0045] For this purpose, the inspection device preferably has at least one emitter for emitting electromagnetic radiation, in particular light including infrared radiation, and at least one detector for detecting radiation emitted by the emitter, in particular light including infrared radiation.

[0046] Furthermore, the test device comprises means suitable for carrying out the steps of the method according to the invention and / or a measuring device and / or an evaluation device.

[0047] According to another aspect, which may also be realized independently, the present invention relates to an examination device for medical examination of animals. This examination device is especially designed for blood pressure measurement. Furthermore, the examination device is preferably designed and / or suitable for examination of animals, preferably of the superfamily Felidae (cat-like) or superfamily Canidae (dog-like), in particular of the family Felidae (cats) or the family Canidae (dogs), particularly preferably of the subfamily Felinae (small cats) or the subfamily Caninae (true dogs), in this family in particular of the family Canidae (wolf-like and jackal-like), particularly preferably of the family Canidae, using one leg of a domestic cat or a domestic dog.

[0048] However, the examination device according to the invention is in principle also suitable for medical examinations in any animal, and in particular in humans, in particular for blood pressure measurements.

[0049] The examination apparatus comprises a sensor device for optical examination of the arterial blood flow of an animal. The examination apparatus is preferably designed for transcutaneous and / or non-invasive examination of blood flows and / or animals. The sensor device and / or the examination apparatus is particularly preferably designed for performing photoplethysmography.

[0050] The sensor device comprises one or more emitters of the same type for emitting electromagnetic radiation and a plurality of detectors of the same type for detecting the radiation emitted by the emitters, the emitters and detectors forming a plurality of sensors of the same type.

[0051] According to the present invention, the inspection device is provided with a controller designed to select a sensor or a subset of sensors. This results in a highly reliable, rapid, and accurate inspection, particularly for blood pressure measurement.

[0052] The sensors preferably each have a plurality of emitters. This results in a highly reliable and accurate inspection, particularly for blood pressure measurement.

[0053] Alternatively or additionally, each emitter is part of a plurality of sensors. By doing so, the number of necessary emitters can be reduced and / or kept low, simplifying the design of the inspection device and making the inspection device more cost-effective.

[0054] Preferably, each sensor has a sensor area, the sensor areas of the sensors are each in a different position, together form a sensing area, each sensor area forms a different sub-area of the sensing area, and the different sub-areas of the sensing area can be selected by the controller. In particular, this makes it possible to omit the very precise positioning and / or fixing of the legs with respect to the sensor and / or the sensor device. Therefore, an inspection that is very comfortable and stress-free for the animal becomes possible. This results in a highly reliable and accurate inspection, particularly for blood pressure measurement.

[0055] The inspection device and / or the controller are preferably designed to execute the method according to the present invention. The inspection device preferably has means adapted to execute the method according to the present invention.

[0056] According to another aspect, the present invention relates to a computer program comprising instructions that, when executed by a computer program, cause an inspection device to execute the steps of the method.

[0057] According to another aspect, the present invention relates to a computer-readable storage medium storing a computer program or storing instructions that cause an inspection device to execute the steps of the method during execution.

[0058] As a result, the present invention makes it possible to measure blood pressure in animals, particularly in animals that, as has been shown in experience, have a high motility and / or low stress tolerance with respect to manipulation of the animal's body, as is the case in particular with domestic dogs and cats.

[0059] Here, up to now, blood pressure measurements have always been very stressful for the animal. The present invention solves this problem in a completely different way to known approaches where the animal is immobilized and / or the sensor technology is immobilized on the animal. The present invention provides a solution in an unpredictable and surprising way by combining measures that do not require movement restrictions but at least basically do not restrict the freedom of movement. Instead of immobilizing the animal, possible measurement problems caused by possible movements of the animal during the examination are technically solved. In particular, so-called movement artifacts, i.e. measurement inaccuracies and measurement errors caused by movements, are eliminated and / or compensated for.

[0060] To achieve this goal, different measures are described and / or applied, which can be realized individually but which, however, interfere with each other and thus allow in a synergistic way a particularly reliable and equally stress-free blood pressure measurement.

[0061] Thus, on the one hand, it is preferably intended that the position of the animal, in particular the leg position, is not strictly given, instead multiple sensors are used and the sensor suitable for the measurement can be selected.

[0062] This is preferably combined with further means, each of which can be implemented separately and combined in a particularly advantageous manner in order to finally determine curve characteristics from the measured curve and in particular to measure the blood pressure on the basis of the curve characteristics.

[0063] A particularly advantageous and basis for some of the further measures is the subdivision or division of the signal or curve into curve sections on the basis of the simultaneously determined heart rate curve. Another basis for most of the proposed measures is the averaging between the curve sections.

[0064] Furthermore, there is also a choice between several alternative results determined in particular on the selection of suitable curve sections and / or on the curve characteristics and / or on filter means and / or on statistical methods. In particular, these and further means described in detail lead to the conclusion that it is sufficient to simply place one or more legs on or at the sensor device and / or to place the animal on the testing apparatus in order to achieve a meaningful determination of the curve characteristics and a reliable blood pressure measurement resulting therefrom, which previously did not seem possible in this form.

[0065] An "animal" in the sense of the present invention is preferably a vertebrate, in particular a mammal, particularly preferably a terrestrial mammal. In particular, the term "animal" in the sense of the present invention also includes humans. Preferably, the animal to be examined has legs. Preferably, the animal to be examined is an animal of the Feloidea (cat-like) or Canoidea (dog-like), in particular an animal of the Felidae (cat) or Canidae (dog), particularly preferably an animal of the family Felinae (small cats) or Caninae (true dogs), in this family in particular an animal of the family Canidae (wolf-like and jackal-like), particularly preferably a domestic cat or a domestic dog.

[0066] An "emitter" in the sense of the present invention is preferably a structure that emits or is designed to emit electromagnetic radiation, in particular in the optical and / or infrared range. Preferably, the emitter is formed by a light-emitting diode, a laser diode or generally a light-generating element. However, the emitter can also be formed by the end of an optical fiber, at least as far as the position of the emitter is concerned, from which emerges the light guided by the optical fiber. From one point of view, the combination of the associated light source and light guide is the emitter. In principle, therefore, the term "emitter" in the sense of the present invention is preferably understood in a broad sense.

[0067] A "detector" in the sense of the present invention is preferably a structure designed to detect electromagnetic radiation, especially in the light and / or infrared range. Preferably, the detector is formed by a photodiode. In principle, however, the detector can also be formed by another structure designed especially for the detection of electromagnetic radiation emitted by an emitter, for example a photocathode, a photocell, a CCD sensor or the like. The detector can also have a light guide having one end on which the light guided by the light guide can enter. In this case, at least as far as the position of the detector is concerned, the end of the light guide is the detector.

[0068] The "radiation area" of an emitter in the sense of the present invention is preferably the area in which the radiation emitted by the emitter reaches or can reach. Preferably, the emitter emits radiation in a certain direction, for example in a certain angular range. The radiation area is therefore preferably defined or limited by one or more radiation angles. The radiation area may be essentially conical.

[0069] The "detection area" of a detector in the sense of the present invention is preferably the area in which radiation reaches or can reach the detector. The detection area is preferably defined or limited by one or more detection angles. The detection area may be essentially conical.

[0070] A "sensor" in the sense of the present invention is preferably a combination of at least one emitter and at least one detector. In particular, a detector together with one or more emitters forms a sensor in the sense of the present invention. A sensor preferably comprises precisely one detector and at least one emitter. The emitter is designed to emit electromagnetic radiation having a wavelength that the detector is sensitive to and / or is capable of detecting this electromagnetic radiation.

[0071] A "sensor area" of a sensor in the sense of the present invention is preferably an area that can be detected / sensed by the sensor or where a measurement can be performed by the sensor. In particular, the sensor area is the overlapping area of ​​the emission area of ​​the emitter and the detection area of ​​the detector of the sensor. The sensor area can be formed by a continuous area or by a number of disconnected or separated areas.

[0072] A "sensor device" in the sense of the present invention is preferably a device having one or more sensors. In particular, the sensor device is a device for optical examination of animal body parts. The sensor device is in particular designed to perform photoplethysmography.

[0073] A "sensing area" of a sensor device in the sense of the present invention is preferably an area detectable / sensible by the sensor device and / or the emitter and / or the detector. The sensing area is in particular an overlapping area of ​​the emission area of ​​the emitter and the detection area of ​​the detector. Preferably, the sensing area is formed by one or more overlapping emission areas and one or more detection areas. The sensing area can be linked or alternatively formed by several separate areas. In particular, the sensing area can be formed by one or more overlapping areas of essentially conical emission and detection areas.

[0074] A "periodic" arrangement of emitters and / or detectors in the sense of the present invention is preferably an arrangement in which the emitters and / or detectors are arranged in an at least substantially equally spaced repeating structure, such periodicity may in particular exist in one or more mutually orthogonal directions.

[0075] An "optical examination" in the sense of the present invention is preferably an examination in which an animal's body part is irradiated with electromagnetic radiation in the optical and / or infrared range visible to humans, in particular with a wavelength between 380 nm and 1400 nm, and the radiation reflected and / or scattered by and / or transmitted through the body part is measured by a detector. The optical examination is preferably a reflectometric examination. Results can then be derived from the reflected, scattered and / or transmitted radiation, for example regarding arterial blood flow. In particular, electromagnetic radiation of a defined wavelength or a defined wavelength range is used for the optical examination. Particularly preferably, the optical examination is a non-invasive and / or percutaneous examination of the interior of the body.

[0076] "Photoplethysmography" in the sense of the present invention is a method for optically examining the arterial blood flow of an animal. In particular, photoplethysmography is a method for non-invasive optical examination, in which an animal's body part is irradiated with electromagnetic radiation, in particular with the range visible to humans and / or with the infrared range, and the radiation scattered and / or (in particular diffusely) reflected and / or transmitted by the body part is measured with a detector. The proportion of reflected and / or scattered and / or transmitted, in particular reflected or transmitted electromagnetic radiation in the direction of the detector, depends, inter alia, on the arterial blood flow, in particular on the arterial blood volume and / or on the oxygen saturation of the arterial blood. Preferably, the fluctuations in the arterial blood flow and / or the changes in the arterial blood volume and / or the changes in the oxygen saturation change the signal measured by the detector, such that the fluctuations in the measurement signal and / or in the course of the measurement signal make it possible to draw conclusions about the arterial blood flow. Pulse oximetry is therefore also (extended) photoplethysmography in the sense of the present invention.

[0077] In the sense of the present invention, pulse oximetry includes at least one photoplethysmography. In pulse oximetry, the oxygen content in blood is determined, where two photoplethysmographies are carried out in particular simultaneously to determine the oxygen content, and these two photoplethysmographies use different wavelengths. From the different absorption rates at the two wavelengths, the oxygen saturation of blood can be determined.

[0078] A "photoplethysmogram" within the meaning of the present invention is in particular a curve that is recorded or measured during the performance of photoplethysmography.

[0079] However, optical examinations are also known from the prior art, for example for determining the oxygen content in the blood, which do not represent or include photoplethysmography. In particular, the methods of cerebral oximetry and tissue oximetry do not include photoplethysmography. These methods are also not suitable for examining arterial blood flow, in particular due to the wavelength of the electromagnetic radiation used.

[0080] A "cardiogram" in the sense of the present invention is preferably a curve representing the activity of the animal's heart. Particularly preferably, the cardiac curve is recorded electrically, in particular by electrodes in contact with the animal's skin, and / or as an electrocardiogram. In principle, however, other methods for recording the cardiac curve are also conceivable, for example an impedance cardiogram or an acoustic recording, so that the cardiac curve is a phonocardiogram.

[0081] A "detection element" in the sense of the present invention is preferably an element for detecting the cardiac activity of an animal. The detection element is particularly suitable or designed for recording a cardiac curve. The detection element is preferably formed by an electrode. However, the detection element can also be formed by or have a microphone or other sound sensor or the like.

[0082] "Arterial blood flow" in the sense of the present invention preferably refers to the flow of blood through an artery. An artery is in particular a blood vessel that carries blood away from the heart. In particular, the arterial blood flow is the blood flow of the animal being examined.

[0083] "Blood pressure" in the sense of the present invention is preferably the pressure (force per area) of blood in a blood vessel, in particular in the blood vessel of a test animal. The blood vessel is preferably an artery. Preferably, the blood pressure is the aortic blood pressure. The blood pressure can be systolic, diastolic and / or mean blood pressure. In particular, in the context of the present invention, it has surprisingly been shown that the proposed method and / or examination device can also be used for diastolic blood pressure measurement. However, this is not necessary.

[0084] A "curve" in the sense of the present invention is preferably a time course of a signal measured by a detector or sensor. The term "curve" also includes data-technical equivalents such as individual data points which (together) represent or correspond to a course. The curve is preferably a time course over several heartbeats.

[0085] A "curve section" in the sense of the present invention is preferably also a section or part of the curve, i.e. in particular also the time course of a signal measured by a detector or sensor. In particular, the curve section is a section of the curve that corresponds to a heart beat, in particular starting at the time of a heart beat and preferably ending at the time of a subsequent heart beat.

[0086] A "curve containing information about the arterial blood flow" in the sense of the present invention is in particular a curve from which results can be drawn concerning the arterial blood flow, in particular the arrival of a pulse wave, the changes in the blood volume in the artery, the changes in the oxygen saturation of the blood in the artery or the like. A photoplethysmogram is a particularly preferred example of a curve containing information about the arterial blood flow.

[0087] A "curve feature" in the sense of the present invention is preferably a feature of the curve and / or of a section of the curve, which contains information, in particular about the arterial blood flow. The curve feature is preferably a feature related to and / or correlated with the pulse wave transit time and / or the blood pressure. In particular, the curve feature is a feature by means of which the blood pressure can be measured. The curve feature is particularly preferably a feature of the curve and / or of a section of the curve, which corresponds to the course and / or the shape of the curve and / or of the curve section and / or contains information about the shape of the curve and / or of the curve section. For example, the curve feature can be the position of the (absolute) extrema, the distance between the (absolute) extrema, the position or absolute value of the (maximum) gradient, the distance between the extrema and / or the zero points of the first and / or second derivative of the curve, or a feature of the Fourier transform of the curve.

[0088] Particularly preferably, the characteristic of the curve corresponds to the pulse wave transit time.

[0089] "Pulse wave transit time" in the sense of the present invention is preferably the time required for a pulse wave to travel a distance in the vascular system. Here, the pressure wave originating from the heart and passing through the artery due to the heartbeat is referred to as a pulse wave. The speed of this pressure wave is in particular faster than the flow speed when blood flows through the artery. Pulse wave transit time is often abbreviated as "PTT". In particular, in the present invention, the term pulse wave transit time includes the heartbeat and the time until the pulse wave caused by this heartbeat reaches a specific location in the artery, i.e. the time required for the pulse wave to travel the distance from the heart to the location of the artery. However, preferably, the term pulse wave transit time also includes the time distance until the pulse wave reaches the first location and the time distance until the pulse wave reaches the second location.

[0090] "Pulse Wave Velocity" in the sense of the present invention is preferably the quotient between the distance traveled by a pulse wave and the pulse transit time required by the pulse wave to travel this distance. Pulse Wave Velocity is often abbreviated as "PWV".

[0091] A "subset" in the sense of the present invention is preferably a subset that does not include all the elements of a proper subset, in particular a superset, thus assigned to the subset. In particular, a subset of sensors of a sensor device is a set of sensors that does not include or has all the sensors of the sensor device.

[0092] "Transcutaneous" testing in the sense of the present invention is preferably testing through the skin. In optical transcutaneous testing, the inside of the body is irradiated through the skin with electromagnetic radiation, preferably in the optically visible (for humans) and / or infrared range, and the scattered, transmitted and / or reflected parts thereof are detected.

[0093] A "non-invasive" test within the meaning of the present invention is preferably a test in which the animal being tested is not injured or harmed.

[0094] A "resampling method" in the sense of the present invention is preferably a method, in particular a mathematical and / or statistical method, in which the statistical properties of a "sample statistic", such as an estimator or a test statistic, are determined on the basis of repeated drawing of samples, so-called sub-samples, from an initial sample. A "sample statistic" in this sense is preferably any measurable function of the random variables of the sample, the statistic being preferably used for statistical purposes. Preferably, in a resampling method, the sample statistic is repeatedly calculated on the basis of the drawn sub-samples, in particular the results being used to study their distribution properties.

[0095] The above mentioned aspects and features, as well as further aspects and features emerging from the claims and the following description, can be realized independently of one another and in different combinations.

[0096] Further advantages, features, characteristics and aspects of the invention emerge from the following description of preferred embodiments based on the claims and the drawings. [Brief description of the drawings]

[0097]

Figure 1

Figure 2

Figure 3

Figure 4

Figure 5

Figure 6

Figure 7

Figure 8

Figure 9

Figure 10

Figure 11

Figure 12

Figure 13

Figure 14

Figure 15

[0098] In the schematic drawings, which are not necessarily to scale, the same reference numerals are used for identical or similar parts, and corresponding or equivalent features and advantages can be obtained even if repeated description is omitted.

[0099] FIG. 1 is a schematic top view of the inspection device 1. As shown in FIG.

[0100] The examination device 1 is preferably designed for medical examination, in particular for measuring blood pressure BP, of an animal T, in particular of an animal T having a leg 2, preferably of a feline animal T, particularly preferably of a domestic cat.

[0101] In principle, however, the examination device 1 is suitable for medical examination of any animal T, in particular humans, in particular animals T in which the blood pressure BP can be measured. Examination with the examination device 1 is particularly advantageous if the animal T has legs or the like.

[0102] However, the testing device 1 may also be designed and / or suitable for medical testing of other animals T, in particular domestic animals such as dogs, mice, rats, rabbits, guinea pigs or the like, in particular for measuring blood pressure BP, and / or may be specifically adapted for testing of these animals T.

[0103] The blood pressure BP may be a systolic, diastolic and / or mean blood pressure. In particular, it has been surprisingly shown in the context of the present invention that the proposed method and / or examination device can also be used to measure the diastolic blood pressure BP. However, this is not essential.

[0104] In FIG. 2, a testing device 1 according to the present invention is shown in a schematic perspective view with an animal T placed thereon.

[0105] Preferably, the test device 1 is designed as a support for at least one leg 2 or other part of the body of an animal T, in particular a part similar to a leg, such as a hand or a finger.

[0106] Particularly preferably, the examination device 1 and / or the support are designed so that the animal T to be examined can be completely placed and / or positioned on the examination device 1 and / or the support, in particular so that all legs of the animal T can be positioned on the examination device 1. However, this is not necessary. In principle, the examination device 1 can also be designed so that only one or more legs 2 can be placed or positioned on the examination device 1.

[0107] The inspection device 1 is preferably designed as a plate or mat, or as a mat-like or plate-like device, or in the form of a mat or plate. In particular, a plate or mat is understood to be a device whose width and length are more than a multiple of its height. A plate is preferably understood to be an at least substantially rigid device. A mat is preferably understood to be an at least partially flexible device. For example, if the inspection device 1 is designed as a mat, the inspection device 1 can be at least partially rollable and / or foldable.

[0108] Preferably, the test device 1 has a rest surface 3. An animal T, in particular a domestic dog, a domestic cat or another animal T of equal or smaller size, can be placed preferably completely on the rest surface 3.

[0109] Preferably, the inspection device 1 and / or the resting surface 3 are at least essentially flat and / or planar.

[0110] Preferably, the inspection device 1 has a mounting surface 3 on one of its upper surfaces and / or the mounting surface 3 is formed by the upper surface of the inspection device 1 or a part thereof.

[0111] The rest surface 3, in its use position, in particular during testing, is preferably at least substantially horizontal or forms a horizontal surface. The use position is a preferred position of the testing device 1 in which an animal T can be placed on the testing device 1 for testing. The use position is particularly shown in FIG. 2.

[0112] The inspection device 1 and / or the rest surface 3 preferably have a width B greater than 20 cm, preferably greater than 40 cm and / or less than 80 cm, preferably less than or equal to 60 cm.

[0113] The inspection device 1 and / or the rest surface 3 preferably have a length L greater than 40 cm, preferably greater than 60 cm and / or less than 120 cm, preferably less than 80 cm. In principle, different widths B and / or different lengths L of the inspection device 1 and / or the rest surface 3 are also conceivable.

[0114] Preferably, the testing device 1 is intended to contact the leg 2 and / or body part on one side only and / or to be stationary or positioned on one side only during testing. Therefore, the testing device 1 is preferably designed to contact the animal T and / or its leg 2 on one side.

[0115] The test device 1 preferably does not have fixing and / or fastening means. Preferably, the test device 1 is not designed to clip onto the leg 2. Preferably, the test device 1 does not have a clip for attachment to the leg 2 and does not have a cuff for application to the leg 2 or other fixing or fastening means for attaching, fixing or fastening the test means, such as sensors or electrodes, to the animal T. In contrast, it is preferred that the test device 1 has a contact surface and a rest surface 3, by which the test can be performed when the leg 2 or a body part is placed or positioned on the device.

[0116] The design of the examination device 1 as a support and / or rest surface 3 for the animal T makes the examination particularly comfortable and therefore stress-free for the animal T. Preferably, it is not intended to fix the animal T to the examination device 1 or to attach or fix parts of the examination device 1, such as sensors or the like, to the animal T. Such methods would cause stress to the animal T, making the examination uncomfortable for the animal T, and it has been shown that stress also affects the blood pressure BP. In contrast, the design of the examination device 1 according to the present invention allows for an extremely comfortable and stress-free examination for the animal T.

[0117] Preferably, the test device 1 or the mounting surface 3 is designed so that the animal T can move freely on the test device 1 and / or the mounting surface 3.

[0118] Through the design of the inspection device 1, which will be described in more detail below, particularly the design and / or arrangement of the sensor device 4 and / or the electrodes 15, it is achieved that the inspection of the animal T, particularly highly reliable and / or accurate blood pressure measurement, can be carried out without avoiding the fixation of the animal T, or can be carried out without fixing the animal T, or can be carried out or made possible when the animal T moves during the inspection by the inspection device 1.

[0119] The inspection device 1 preferably has a sensor device 4. The sensor device 4 is designed to optically inspect the arterial blood flow BF of the animal T, particularly to record a curve K containing information regarding the arterial blood flow BF of the animal T. In particular, the sensor device 4 is designed to perform photoplethysmography and / or to record a photoplethysmogram.

[0120] A curve K containing information regarding the arterial blood flow BF is shown as an example in FIG. 9 and will be described in detail later.

[0121] The sensor device 4 and / or the inspection device 1 are preferably designed to enable or allow the movement of the animal T during the inspection, and / or to enable a highly reliable and accurate inspection, particularly blood pressure measurement, and / or to reduce, avoid and / or compensate for motion artifacts.

[0122] The inspection device 1 preferably has the sensor device 4 in the region of the placement surface 3. Thus, when the leg 2 or the body part is placed on the surface, the inspection by the sensor device 4 can be carried out.

[0123] The sensor device 4 is preferably arranged on or integrated into the testing apparatus 1 in such a way that the leg 2 of the animal T can be located at, above and / or in the vicinity of the sensor device 4, particularly when the animal T is located on the testing apparatus 1 and / or on the resting surface 3. In the example shown in Fig. 1, the sensor device 4 is arranged in such a way that the left front leg 2 of the animal T can be located above the sensor device 4 without any problems and in a comfortable and / or natural position for the animal T. However, the sensor device 4 can also be provided in other positions.

[0124] 2 and 7 show, by way of example, the positioning of the leg 2 during testing with the sensor device 4. For testing with the sensor device 4, the leg 2 is preferably positioned such that one or preferably several paw pads of the leg 2 are in contact with the sensor device 4, in particular the cover 14 and / or the electrodes 15.

[0125] The examination device 1 may also have several, in particular two, sensor devices 4, for example a sensor device 4 for the left front leg 2 and a sensor device 4 for the right front leg 2 of the animal T to be examined. In this case, the sensor devices 4 are preferably of similar or identical design. This is in particular shown in FIG.

[0126] The sensor device 4 is preferably designed for the reflectance measurement of the arterial blood flow BF.

[0127] The sensor device 4 has at least one emitter 5 which emits electromagnetic radiation R (particularly light including ultraviolet and / or infrared radiation) and preferably at least one detector 6 which detects the electromagnetic radiation R (particularly light including ultraviolet and / or infrared radiation) emitted by the emitter 6.

[0128] The emitter 5 is preferably designed as a light-emitting diode or a laser diode.

[0129] The detector 6 is preferably designed as a photodiode.

[0130] Preferably, the emitters 5 can be activated and / or deactivated and / or switched on and / or off separately, in particular by means of MOSFETs assigned to the emitters 5 .

[0131] Figures 3 and 4 show examples of schematic top views of sensor devices 4 in different embodiments. The sensor devices 4 according to Figures 3 and 4 are basically of the same or similar design and differ mainly only in the number of emitters 5 and detectors 6.

[0132] Preferably, the sensor device 4 has a plurality of emitters 5 and a plurality of detectors 6. In principle, however, the sensor device 4 can also have exactly one emitter 5 and exactly one detector 6, or exactly one emitter 5 and multiple detectors 6, or multiple emitters 5 and exactly one detector 6.

[0133] However, preferably, the sensor device 4 has at least nine, and in the example shown in Figures 1 and 3 exactly nine emitters 5 and / or at least four, and in the example shown in Figures 1 and 3 exactly four detectors 6.

[0134] The emitter 5 and the detector 6 are preferably arranged in the same plane.

[0135] The emitters 5 and detectors 6 are preferably arranged in a repeating and / or repetitive structure. Particularly preferably, the emitters 5 and detectors 6 are arranged in a periodic or cyclic structure.

[0136] Preferably, the emitters 5 and detectors 6 are arranged in the form of a matrix with (virtual) rows and columns or in a matrix or array. Preferably, the matrix or array has three or more rows and / or three or more columns.

[0137] The emitters 5 and detectors 6 are preferably arranged in an alternating fashion. Preferably, the emitters 5 and detectors 6 form one or more, in particular linear, rows, with the emitters 5 and detectors 6 arranged in an alternating fashion in each row. The rows may also be curved and / or may mimic an organic shape, such as a leg 2.

[0138] Preferably, each detector 6 (except for emitters 5 and / or detectors 6 which, as the case may be, are located at the outermost and / or edge of the sensor device 4 and / or row and / or matrix) is (directly) surrounded by a plurality of emitters 5 and / or each emitter 5 is (directly) surrounded by a plurality of detectors 6.

[0139] Particularly preferably, several emitters 5 are assigned to each detector 6 or vice versa. This preferably allows multiple use of emitters 5 and / or detectors 6.

[0140] Emitters 5 and detectors 6 are assigned to one another, in particular if they are arranged in such a way that radiation R emitted by the emitters 5 reaches or can reach the detector 6, in particular after scattering or reflection on the legs 2. Particularly preferably, these emitters 5 are assigned to the detector 6 which has a minimum distance D to this detector 6 and / or is (directly) adjacent to this detector 6. Likewise, in particular, these detectors 6 are assigned to the emitter 5 which has a minimum distance D to this emitter 5 and / or is (directly) adjacent to this emitter 5.

[0141] The distance D between the emitter 5 and the detector 6 is understood in particular as the distance between the center point or geometric center of the emitter 5 or its light-emitting surface and the center point or geometric center of the detector 6 or its detection surface. Preferably, the emitter 5 and the detector 6 are formed by components and / or rectangular components of different sizes, as also shown by the rectangles of different sizes in Figures 1 to 4, and the emitter 5 and the detector 6 are arranged such that the center points or geometric centers of gravity of these components, shown as dots in Figure 3, have the same distance D from each other.

[0142] Preferably, the emitters 5 assigned to the detectors 6 have the same distance D to the detectors 6. Similarly, this also applies to the detectors 6 assigned to the emitters 5.

[0143] The distance D is preferably greater than 2 mm, more preferably greater than 3 mm, in particular greater than 4 mm, and / or less than 10 mm, preferably less than 8 mm, in particular less than 7 mm. The distance D is particularly preferably between 4 mm and 6 mm.

[0144] Preferably, the emitters 5 of the sensor devices 4 are of the same design or type. Particularly preferably, the emitters 5 of the sensor devices 4 are of identical construction and / or are designed to emit light of the same wavelength or in the same wavelength range.

[0145] Preferably, the detectors 6 of the sensor device 4 are of the same design or type. Particularly preferably, the detectors 6 are of identical construction and / or design, in particular for detection of the same radiation R or wavelength emitted by the emitter 5.

[0146] The sensor device 4 is preferably designed for inspection with electromagnetic radiation R in the infrared range. Particularly preferably, the emitter 5 is designed for the emission of infrared radiation and / or the detector 6 is designed for the detection of infrared radiation.

[0147] Infrared radiation is in particular electromagnetic radiation R having a wavelength between 780 nm and 1400 nm.

[0148] Preferably, the emitter 5 is designed for the emission of electromagnetic radiation R having a wavelength above 900 nm and / or below 1200 nm or 1100 nm. Particularly preferably, the emitter 5 is designed for the emission of electromagnetic radiation R having a wavelength above 920 nm and / or below 960 nm, in particular at (approximately) 940 nm. However, alternatively or additionally, it is also possible for the emitter 5 or a subset of the emitters 5 to be designed to emit electromagnetic radiation R having a wavelength above 1030 nm and / or below 1070 nm, in particular at (approximately) 1050 nm.

[0149] The detector 6 is preferably designed to detect the radiation R emitted by the emitter 5 .

[0150] Preferably, the sensor device 4 comprises at least one, preferably several, sensors 7. The sensor 7 comprises or is formed in this way at least one emitter 5 and at least one detector 6. Particularly preferably, the sensor 7 comprises exactly one detector 6 and several emitters 5, exactly four emitters 5 in the example shown in figures 3 and 4.

[0151] Preferably, the emitters 5 of the sensors 7 are arranged symmetrically around the detector 6 of the sensors 7 and / or the emitters 5 of the sensors 7 have the same distance D to the detector 6 of the sensors 7 .

[0152] In particular, the sensor device 4 comprises a number of sensors 7 which are of the same type or kind, in particular of identical construction. Particularly preferably, all sensors 7 of a sensor device 4 are identical. However, other solutions are also possible here.

[0153] In the illustrated example shown in Fig. 3, the sensor device 4 has exactly four sensors 7, one of which is shown in dotted lines in Fig. 2, and a number of sensors 7 are shown in dashed lines in Fig. 4.

[0154] Preferably, an emitter 5 is assigned to a number of sensors 7 and / or each emitter 5 forms part of a number of sensors 7 (apart from the emitters 5 arranged at the outermost edge of the sensor device 4). In particular, each emitter 5 is assigned to a row or column of adjacent detectors 6 and / or to the detectors 6 having a minimum distance D. In the illustrated example, an emitter 5 (apart from the emitters 5 arranged at the edge) is assigned to each of four detectors 6.

[0155] In the illustrated embodiment, a number of emitters 5 are assigned to each detector 6, and these emitters 5 (except the outermost emitters 5 or the emitters 5 arranged at the edges) are assigned in turn to each of the detectors 6. In this way, a number of sensors 7, in particular of the same kind or type, are formed, and the emitters 5 (except the outermost emitters 5 or the emitters 5 arranged at the edges) are each part of the number of sensors 7. In the example shown in FIG. 3, the emitter 5 arranged in the center of the sensor device 4 is assigned to each of the four detectors 6. The emitters 5 arranged at the top, bottom, leftmost and rightmost parts in FIG. 3 are each assigned to only one detector 6. The remaining four emitters 5 in FIG. 3 are each assigned to two detectors 6. In this way, four sensors 7, in particular of the same kind or type, are formed in FIG. 3.

[0156] 3 shows the basic design of the sensor device 4 or the basic arrangement of the emitters 5, detectors 6 and / or sensors 7, the sensor device 4 preferably has a significantly larger number of emitters 5, detectors 6 and / or sensors 7, as shown by way of example in FIG. 4. In this way, a large sensor area can be realized, so that the exact positioning of the leg 2 for the examination and / or blood pressure measurement is not critical and a larger area can be examined by the sensor device 4. This results in less stress on the animal T during the examination, since the leg 2 of the animal T does not have to be fixed, and a quicker, more accurate, more reliable and as comfortable as possible for the animal T to be examined, in particular the blood pressure measurement, can be realized.

[0157] The sensor device 4 preferably comprises more than 30, in particular more than 60 and / or less than 500, preferably less than 200, more preferably less than 100, in particular less than 100, particularly preferably about 80 emitters 5.

[0158] Preferably, the sensor device 4 comprises more than 20, preferably more than 40 and / or less than 500, preferably less than 200, in particular less than 100, particularly preferably about 60 detectors 6 .

[0159] Preferably, the detector 6 together with a plurality of emitters 5 form a sensor 7, so that the number of sensors 7 corresponds to the number of detectors 6. However, when the emitters 5 together with a plurality of detectors 6 form a sensor 7, the number of sensors 7 preferably corresponds to the number of emitters 5.

[0160] The sensor devices 4 and / or the matrix of emitters 5 and detectors 6 preferably have a size of 10 cm 2 Above 20cm 2 More than 30 cm, particularly preferred 2 More than 40 cm, very particularly preferably 2 and / or 200cm 2 Less than 150cm, preferably 2 Less than 100cm, more preferably 2 Less than 80cm 2 It has the following area:

[0161] Preferably, the areal density of the emitters 5, the areal density of the detectors 6, the areal density of the sensors 7, and / or the common areal density of the emitters 5 and the detectors 6 is less than 0.5 / cm 2 preferably greater than 1 / cm 2 Above 2 / cm 2 and / or 40 / cm 2 Less than 20 / cm 2 Less than 10 / cm 2 Here, the number of emitters 5 and / or detectors 6 and / or sensors 7 per area is especially denoted as areal density.

[0162] The number, arrangement, area and / or area density of the sensor devices 4, emitters 5, detectors 6 and / or sensors 7 preferably allow reliable and accurate tests, in particular photoplethysmography and / or blood pressure BP measurements, to be performed without fixing the leg 2 of the animal T relative to a test means such as a sensor, thus allowing the animal T to move freely relative to the sensor device 4 during the test. This results in a particularly comfortable and stress-free test for the animal T and improves the measurement accuracy.

[0163] The emitters 5 and / or the detectors 6 are preferably each divided into or preferably form a number of groups, which in particular are separate from one another and / or are connected separately.

[0164] Preferably, the emitters 5 are divided into two groups and / or the emitters 5 form two groups.

[0165] Preferably, the detectors 6 are divided into and / or form five groups.

[0166] The emitters 5 within a group and / or the detectors 6 within a group are preferably connected or interconnected in series.

[0167] FIG. 5 is a schematic cross-section through the sensor device 4.

[0168] FIG. 6 shows the sensor device 4 in a schematic exploded view.

[0169] The sensor device 4 preferably comprises a limiting device 8 .

[0170] At this point, it should be noted that the limiting device 8 and the associated features and advantages can in principle be realised independently of the above-mentioned design of the sensor device 4. In particular, the limiting device 8 can also be advantageous for a sensor device 4 having exactly one emitter 5 and exactly one detector 6. As a result, in the following, the terms "emitter" and "detector" are preferably used in the singular. Of course, this description also applies to designs of sensor devices 4 having multiple emitters 5 and / or multiple detectors 6, in particular to sensor devices 4 designed as described above.

[0171] The limiting device 8 is preferably designed to determine, define and / or limit an emission area 9 of the emitter 5, a detection area 10 of the detector 6, a sensor area 11 of the sensor 7 and / or a sensing area 12 of the sensor device 4. In particular, the limiting device 8 is designed as an aperture for the emitter 5 and / or the detector 6.

[0172] For this purpose, the limiting device 8 in the shown example comprises or is formed by a barrier 13, which will be explained in more detail below. Alternatively or additionally, however, the limiting device 8 can comprise one or more lenses, not shown, in particular focusing lenses, which in particular focus the radiation R and thereby result in a corresponding limiting of the emission region 9 and / or the detection region 10.

[0173] The emission area 9 of the emitter 5 is generally the area within which radiation R can be emitted by the emitter 5. For example, the emission area 9 of the emitter 5 may be at least essentially conical and / or defined by one or (particularly in the case of a non-conical emission area 9) multiple emission angles 9a.

[0174] The detection region 10 of the detector 6 is generally the range over which radiation R can reach the detector 6 and / or the range over which radiation R can be detected by the detector 6. For example, the detection region 10 of the detector 6 may be at least essentially conical and / or may be defined by one or (particularly in the case of a non-conical detection region 10) multiple detection angles 10a.

[0175] Preferably, the emitter 5 and / or the detector 6 necessarily have a certain emission area 9 or detection area 10, respectively. Preferably, this natural emission area 9 and / or detection area 10 is limited or restricted, respectively, by the limiting device 8 or the limiting device 8 is designed for this purpose. The terms "emission area" and "detection area" in the sense of the present invention therefore preferably refer to the emission area 9 or detection area 10 defined or restricted by the limiting device 8, and not to the natural emission area 9 or detection area 10 of the emitter 5 or detector 6 as such.

[0176] The emission region 9 is indicated in Fig. 5 by a V-shaped dotted line originating from the emitter 5. The dotted line represents the boundary of the emission region 9, which is in particular defined by the limiting device 8. In particular, the emission region 9 is an area surrounded or limited by a line.

[0177] The detection area 10 is indicated in Fig. 5 by a V-shaped dotted line originating from the detector 6. The dotted line represents the boundary of the detection area 10, in particular where the limiting device 8 is defined. In particular, the detection area 10 is an area enclosed or limited by a line.

[0178] The emission area 9 of the emitter 5 is preferably limited by a (virtual) line, in particular a line shown in dashed dotted line in Fig. 5, which represents the optical paths of the outermost rays of light that can leave the sensor device 4 as the centre point or geometric centre origin of the emission area of ​​the emitter 5. In particular, the line represents an edge or boundary of the emission area 9. In particular, the emission area 9 is an area enclosed or limited by a line.

[0179] As shown in FIG. 5, when the limiting device 8 is realized by a barrier 13, these outermost beams are the beams that are not blocked by the limiting device 8 as a central point or geometric central origin, so that the lines representing these beams in FIG. 5 are in contact with the edges or corners of the limiting device 8 or barrier 13.

[0180] If the limiting device 8 comprises or is formed by a lens instead of or in addition to the barrier 13, these outermost light rays are the light rays passing from the central point or geometric centre of the light emitting surface of the emitter 5 through the outermost edge of the lens.

[0181] The detection area 10 of the detector 6 is preferably limited by a (virtual) line, in particular the line shown by dashed dotted line in Fig. 5, which represents the optical path of the outermost light rays that can reach the detection surface of the detector 6 from the outside of the sensor device 4, in particular its centre point or geometric centre. In particular, the line represents an edge or boundary of the detection area 10. In particular, the detection area 10 is an area enclosed or limited by a line.

[0182] As shown in Figure 5, when the limiting device 8 is realised by a barrier 13, these outermost rays are the rays that are not blocked by the limiting device 8 and can therefore reach the central point or geometric centre of the detection surface of the detector 6, so that the lines in Figure 5 representing these rays touch the rim or edge or corner of the limiting device 8 or barrier 13.

[0183] If the limiting device 8 comprises or is formed by a lens instead of or in addition to the barrier 13, these outermost light rays are those light rays that can pass from the outside of the sensor device 4 through the outermost edge of the lens to reach the centre point or geometric centre of the detection surface of the detector 6.

[0184] Preferably, the emission angle 9A is the angle between lines (imaginary, in particular outside of which the sensor device 4 extends) representing the boundaries of the emission area 9. This is shown in particular in FIG.

[0185] Preferably, the detection angle 10A is the angle between lines (imaginary, in particular outside of which the sensor device 4 extends) representing the boundaries of the detection area 10. This is in particular shown in FIG.

[0186] In the above definitions of the emission area 9 and the detection area 10, an idealized approach was chosen and reference was made to a central point or geometric center of the emission or detection area, which in reality deviates from point-like and forms an extended area (albeit very small). This makes it possible that in reality the radiation R from the emitter 5 can also reach areas outside the above-defined emission area 9 and / or that radiation R from outside the above-defined detection area 10 can reach the detector 6, in particular as scattered light. However, the above definitions of the emission area 9 and the detection area 10 remain unaffected by this. Moreover, the above-defined emission area 9 and the detection area 10 also represent in reality an area from which a large part of the radiation R emitted by the emitter 5 is emitted and / or an area from which the radiation R can reach the detector 6.

[0187] The sensor area 11 of the sensor 7 is generally an area that can be inspected or sensed by the sensor 7. Preferably, only objects located in the sensor area 11 can be inspected by the sensor 7. In particular, the sensor area 11 of the sensor 7 is an overlapping area of ​​the emission area 9 of the emitter 5 of the sensor 7 and the detection area 10 of the detector 6 of the sensor 7.

[0188] 5, by way of example, arrows indicate how radiation R can pass from emitter 5 to detector 6. The arrows very diagrammatically indicate the path of a light beam emitted by emitter 5 and reaching detection area 10, and thus the area of ​​overlap of emission area 9 and detection area 10, and scattered or reflected by an object not shown in the figure in the direction of detector 6 and thus reaching detector 6.

[0189] In principle, it is possible, deviating from the idealized view chosen here, that in reality objects outside the above-defined sensor area 11 are at least partially detectable or detectable by the sensor 7. On the one hand, this can be done by the fact that, as already mentioned above, in reality small amounts of radiation R can also reach areas outside the defined emission area 9 and / or radiation R from outside the defined detection area 10 can also reach the detector 6. On the other hand, however, it can also happen that objects or parts of objects are detected by the sensor 7 which are located outside the defined sensor area 11, for example in the case of multiple scattering in the object.

[0190] The sensing area 12 of the sensor device 4 is the area that can be inspected and / or detected / sensed by the sensor device 4. In particular, the sensing area 12 comprises or is formed by the emission area 9, the detection area 10 and / or the sensor area 11.

[0191] Preferably, the sensing area 12 is the sum / entire of the sensor areas 11 of the sensors 7 of the sensor device 4 .

[0192] The sensing area 12 may be formed by a continuous / connected area, which is the case when the sensor areas 11 of the sensors 7 of the sensor device 4 overlap.

[0193] However, it is also possible that the sensing area 12 is not connected or is formed by separate or unconnected areas or sensor areas 11. This is the case when at least a part of a sensor area 11 of a sensor 7 does not overlap with another sensor area 11.

[0194] The sensing area 12 preferably has a boundary G. The boundary G is preferably formed by an edge or the entire edge of the sensor area 11. The boundary G is in particular a point or a line where the emission area 9 and the detection area 10 intersect. This is in particular shown in FIG.

[0195] The sensing area 12 and / or its boundary G preferably have a distance X from the sensor device 4. In particular, a (minimum) penetration depth into the leg 2 of the radiation R emitted by the emitter 5 and / or detected by the detector 6 during the test can be achieved or ensured. In particular, this minimum penetration depth or distance X prevents light reflected or scattered from the surface of the leg 2 from reaching the detector 6. This improves the accuracy and reliability of the test, in particular the blood pressure measurement.

[0196] The distance X is preferably the minimum distance of the sensing area 12 or its boundary line G from the sensor device 4. Preferably, as can be seen in particular from Fig. 5, the boundary line G of the sensing area 12 does not extend in a straight line or parallel to the sensor device 4. In a cross-sectional view as shown in Fig. 5, the boundary line G extends in a particularly zigzag manner. This is in particular due to the fact that the sensor area 11 of the sensor 7 preferably increases (in cross-section) in a V-shape with increasing distance from the sensor device 4. As a result, the sensing area 12 preferably has different distances from the sensor device 4 at different positions of the sensor device 4, the distance X being the minimum of these different distances.

[0197] The limiting device 8 is preferably designed such that the distance X of the boundary G of the sensing area 12 from the sensor device 4 is more than 0.5 mm, preferably more than 1 mm and / or less than 10 mm, preferably less than 5 mm, in particular less than 3 mm.

[0198] The limiting device 8 preferably limits the emission angle 9A of the emitters 5 and / or the detection angle 10A of the detectors 6 (particularly in the cross-sectional plane shown in Figure 5) to less than 90°, preferably less than 75°, in particular about 60°. The cross-sectional plane shown in Figure 5 is perpendicular to the plane defined by the matrix of emitters 5 and detectors 6 and intersects the emitters 5 and detectors 6 along the rows or columns of the matrix.

[0199] The limiting device 8 is preferably formed by one or more barriers 13. The barriers 13 are arranged between the emitters 5 and the detectors 6. Preferably, a barrier 13 is arranged between each detector 6 and a respective adjacent emitter 5.

[0200] The barrier 13 is impermeable to the radiation R emitted by the emitter 5, in particular to infrared radiation.

[0201] The barrier 13 is preferably arranged or designed to reach or achieve the above-mentioned distance X of the boundary G of the detection range 8 from the sensor device 4 .

[0202] The dimensions of the limiting device 8 or barrier 13, in particular its height HB and / or width BB, as well as the distance DB of the limiting device 8 or barrier 13 from the emitter 5 and detector 6 and the distance D of the emitter 5 from the detector 6 are preferably matched to one another such that the emission area 9 of the emitter 5 and the detection area 10 of the detector 6 overlap and reach or realize the above-mentioned distance X of the boundary G of the sensing area 12 from the sensor device 4 and / or the above-mentioned emission angle 9A and / or detection angle 10A.

[0203] Preferably, the barrier 13 performs several functions and / or has several sections 13B, 13C which specifically fulfill these functions.

[0204] The function of the barrier 13 is preferably to shield the emitter 5 from the detector 6, in particular in such a way that the radiation R emitted by the emitter 5 cannot reach the detector 6 directly or without intermediate scattering and / or reflection. For this purpose, the barrier 13 preferably has a shielding section 13b. The shielding section 13B is thus preferably designed to shield the detector 6 from the emitter 5 or to prevent direct crosstalk from the emitter 5 to the detector 6. The shielding section 13B is preferably arranged between the emitter 5 and the detector 6. The shielding section 13B preferably extends at least substantially parallel to the main radiation direction of the emitter 5 and / or transversely, in particular at least substantially perpendicularly, to the plane formed by the emitter 5 and the detector 6.

[0205] Another function of the barrier 13 is preferably to limit the emission area 9, the detection area 10, the sensor area 11 and / or the sensing area 12, as already mentioned above. In other words, the barrier 13 and / or parts thereof preferably represent an aperture for the emitter 5 and / or the detector 6. For this purpose, the barrier 13 preferably has an aperture section 13C. The aperture section 13C is preferably designed and / or arranged such that the emission area 9 of the emitter 5 and / or the detection area 10 of the detector 6 is limited or restricted, in particular in the manner mentioned above. The aperture section 13C preferably forms an aperture. In particular, the aperture section 13C preferably extends transversely, preferably at least substantially perpendicularly, to the main emission direction of the emitter 5 and / or at least substantially parallel to the plane formed by the emitter 5 and the detector 6.

[0206] The shielding section 13B and the aperture 13C are preferably designed in one piece and / or are formed by different sections of the same component. In particular, the aperture section 13C can be wider than the shielding section 13B, resulting in a T-shaped cross section of the barrier 13, as shown in Figure 5. However, this is not necessary.

[0207] The restriction device 8 and / or the barrier 13, in particular the aperture section 13C, preferably has a width BB greater than 1 mm, in particular greater than 2 mm and / or less than 5 mm, in particular less than 4 mm. Furthermore, the restriction device 8 and / or the barrier 13 preferably has a height HB greater than 1 mm, preferably greater than 2 mm and / or less than 5 mm, in particular less than 4 mm.

[0208] Preferably, the barrier 13 forms or limits areas 13A that are transparent and / or semi-transparent to the radiation R emitted by the emitter 5 and / or detected by the detector 6. These transparent areas 13A are arranged corresponding to the emitters 5 and detectors 6, respectively, so that the material located in the sensor device 4 above the emitters 5 and detectors 6, respectively, and between or surrounding the transparent areas 13A forms the limiting device 8 and / or the barrier 13. This is shown by way of example in figures 5 and 6.

[0209] The test apparatus 1 and / or the sensor device 4 preferably comprises a barrier element 13D. Preferably, the barrier element 13D comprises or forms one or more barriers 13.

[0210] The barrier element 13D is preferably a one-piece part, in particular a flat and / or plate-like part, having a transparent area 13A.

[0211] The transparent areas 13A are preferably formed by through-holes in the barrier element 13D, but in principle it is alternatively or additionally possible for the transparent areas 13A to be formed by or to comprise a material transparent to the radiation R emitted by the emitter 5 and / or detected by the detector 6, such as glass, plexiglass or the like.

[0212] The restriction device 8 and / or the barrier 13 and / or the barrier elements 13D and / or the transparent areas 13A preferably form a grid or lattice, in particular a grid aperture, which corresponds to the emitters 5 and / or the detectors 6 .

[0213] Preferably, the sensor device 4 has a cover 14 that is transparent to the radiation R emitted by the emitter 5 and / or detected by the detector 6. The cover 14 can be made of glass, plexiglass, transparent plastic or the like.

[0214] Preferably, the cover 14 covers the sensor device 4 completely, continuously and / or without gaps.

[0215] The cover 14 is preferably designed to protect the sensor device 4 and / or the emitter 5 and / or the detector 6 from dirt and / or damage. The cover 14 preferably forms or has an at least substantially flat and / or uniform, in particular smooth, surface for supporting the legs 2.

[0216] Particularly preferably, the distance X of the boundary G of the sensing area 12 from the sensor device 4 is or corresponds to the distance of the boundary G of the sensing area 12 from the cover 14, in particular from the side of the cover 14 facing away from the emitter 5 and / or detector 6.

[0217] Preferably, the examination device 1 comprises one or more detection elements for detecting the cardiac activity of the animal T, in particular for recording the heart rate curve KG.

[0218] The heart rate curve KG preferably represents the activity of the heart, in particular of the animal T examined by the examination device 1, and / or contains information regarding the activity of the heart.

[0219] FIG. 9 is a diagram showing an example of a heart rate curve KG.

[0220] In particular, the heart beats or the times at which the heart beats occur can be read or derived or determined from the heart rate curve KG.

[0221] The heart rate curve KG is preferably an electrocardiogram, but in principle it can also be an impedance cardiogram, a phonocardiogram, a ballistocardiogram or the like.

[0222] The detection element is preferably formed by an electrode 15. In principle, however, the detection element can also be formed by or comprise one or more microphones or other sound sensors or the like.

[0223] Preferably, the test device 1 thus comprises at least one electrode 15, preferably at least two electrodes 15. In the example shown, the test device 1 comprises three electrodes 15. In principle, however, the test device 1 can also comprise a significantly greater number of electrodes 15.

[0224] Preferably, the heart rate curve KG can be recorded by the electrodes 15 and / or the electrodes 15 are designed to record the heart rate curve KG, in particular the heart rate curve KG being an electrocardiogram.

[0225] The electrode 15 is preferably planar and / or layered, in particular made of or comprising an electrically conductive material.

[0226] Preferably, at least one of the electrodes 15 is designed as a tissue electrode. This is shown diagrammatically in FIG. 1 by the hatching of the electrodes 15. Preferably, all the electrodes 15 are designed as fabric electrodes. This has proven to be particularly advantageous for the examination of animals T, such as cats or dogs, since the examination can be made particularly comfortable for the animals T. In particular, it has proven to be easily irritated by metallic and / or shiny surfaces, which can be avoided by using tissue electrodes.

[0227] In the following, the at least two electrodes 15 are referred to as a first electrode 15A and a second electrode 15B in order to better distinguish between them. The electrodes 15A and 15B may be the same or may have different designs.

[0228] Thus, any description making reference to the first electrode 15A preferably also applies to the second electrode 15B, and vice versa.

[0229] Preferably, electrodes 15A, 15B are each designed to contact a leg 2 of animal T. Particularly preferably, the first electrode 15A is designed to contact the left front leg and the second electrode 15B is designed to contact the right front leg.

[0230] Optionally, the test device 1 has a third electrode 15C. The third electrode 15C is preferably designed as a reference electrode or a collector electrode. The third electrode 15C is preferably designed to simultaneously contact multiple parts of the body of the animal T to be tested, in particular multiple legs 2, in particular the two hind legs of the animal T.

[0231] The electrodes 15 are preferably arranged so that when the animal T is placed on the examination device 1 in a natural posture for the animal T, particularly in a sitting or lying position, one leg 2 of the animal T comes into contact with one of the electrodes 15. In this way, the examination can be performed in a particularly comfortable manner for the animal T.

[0232] The arrangement, size and design of the electrodes 15 are preferably adapted to the anatomical structure of the animal T being tested, in particular a domestic cat, so that the test can be carried out in a natural, preferably comfortable, position for the animal T and / or so that the animal T can move freely relative to the electrodes 15 during the test.

[0233] The electrodes 15, in particular the first electrode 15A and the second electrode 15B, are preferably arranged at a distance DE of more than 2 cm, in particular more than 5 cm and / or less than 25 cm, in particular less than 20 cm, particularly preferably less than 15 cm, very particularly preferably about 10 cm.

[0234] The distance DE between two electrodes 15 is referred to in particular as the distance DE between the center points or geometric centers of the electrodes 15 or their surfaces. This is shown diagrammatically in FIG.

[0235] The electrodes 15, in particular the distance DE of the first electrode 15A from the second electrode 15B, are preferably fixed and / or not variable.

[0236] The electrodes 15A, 15B are preferably spaced apart by 10 cm 2 Above 15cm 2 and / or 100cm 2 Less than 80cm 2 Less than 50 cm, particularly preferably 2 having an area of ​​less than

[0237] The third electrode 15C is preferably 50 cm 2 Exceeding 100cm 2 and / or 1000 cm 2 Less than 500cm, preferably 2 Less than 200cm 2 having an area of ​​less than

[0238] The third electrode 15C preferably has an area larger than that of the first electrode 15A and / or the second electrode 15B, in particular an area two or three times larger, and particularly preferably four times larger, than that of the first electrode 15A and / or the second electrode 15B.

[0239] Preferably, the first electrode 15A is arranged on the leg 2, in particular the left front leg or the right front leg, so that a heart rate curve KG can be recorded by the first electrode 15A and simultaneously an optical examination can be performed and / or a curve K, in particular a photoplethysmogram, can be recorded by the sensor device 4.

[0240] FIG. 7 shows, by way of example, a leg 2 positioned so that a heart rate curve KG can be recorded by a first electrode 15A and at the same time optical testing can be performed and / or a curve K can be recorded by a sensor device 4.

[0241] The first electrode 15A is preferably designed as a tissue electrode.

[0242] A tissue electrode is preferably an electrode which comprises or is formed by a tissue. In particular, in the case of a tissue electrode, the contact surface which comes into contact with the body part, and in particular with the leg 2, comprises or is formed by a tissue. The tissue is preferably a conductive tissue, for example a tissue incorporating conductive threads and / or a tissue coated with a conductive layer.

[0243] The first electrode 15A is preferably arranged on the sensor device 4 and / or on the cover 14, particularly preferably on the side of the cover 14 facing away from the emitter 5 and the detector 6. This is shown in particular in figures 5 to 7.

[0244] The first electrode 15A is preferably arranged (only) between the emitter 5 and the detector 6 and / or opposite the barrier 13 in a projection perpendicular to the plane formed by the cover 14 and / or the emitter 5 and the detector 6. Alternatively or additionally, the electrode 15A is transparent to the radiation R emitted by the emitter 5. Thereby, the optical examination of the animal T and / or the leg 2 by the sensor device 4 is not affected by the first electrode 15A.

[0245] The first electrode 15A preferably has areas 16 that are transparent to the radiation R emitted by the emitter 5 and / or detected by the detector 6. These transparent areas 16 are arranged corresponding to the emitter 5 and the detector 6, so that they are located above the emitter 5 and the detector 6, respectively (in the plane of the emitter 5 and / or the detector 6 and / or in a projection perpendicular to the cover 14).

[0246] This is particularly shown in FIGS.

[0247] The transparent area 16 of the first electrode 15A is preferably formed by a through hole in the electrode 15A. In principle, alternatively or additionally, it is possible for the transparent area 16 or the entire first electrode 15A to be formed by or comprise a material that is transparent to the radiation R emitted by the emitter 5 and / or detected by the detector 6.

[0248] The first electrodes 15A and / or the transparent areas 16 preferably form a lattice or grid corresponding to the emitters 5 and / or detectors 6 .

[0249] Optionally, the test apparatus 1 comprises a positioning aid 24. The positioning aid 24 is designed to assist in the correct positioning of the animal T or leg 2 for the test. In particular, the positioning aid 24 is designed to indicate or mark an area for positioning the leg 2 or legs 2, in particular the left front leg and / or the right front leg. The positioning aid 24 is preferably arranged close to the sensor device 4 and / or preferably surrounds the sensor device 4. Alternatively or additionally, the position of one or more of the electrodes 15 can be indicated by the positioning aid 24.

[0250] The positioning aid 24 is preferably formed by a bump or a recess in the inspection device 1 and / or in the rest surface 3. The positioning aid 24 can, for example, be funnel-shaped or have the shape of a funnel.

[0251] However, the positioning aid 24 is merely optional and not required.

[0252] The test device 1 preferably comprises a circuit board 17, in particular a printed circuit board (PCB).

[0253] Preferably, the circuit board 17 holds the sensor device 4 and / or the sensor device 4 is arranged on the circuit board 17 .

[0254] Preferably, the circuit board 17 carries the first and / or second electrodes 15A, 15B, and / or the first and / or second electrodes 15A, 15B are disposed on the circuit board 17. Optionally, the circuit board 17 also carries and / or the third electrode 15C is also disposed on the circuit board 17.

[0255] The circuit board 17 preferably comprises or forms peripherals and / or electrical wiring necessary for the operation of the sensor device 4, in particular the emitter 5 and / or the detector 6 and / or the sensor 7, and the electrodes 15A, 15B, and for the evaluation of the signals measured by the detector 6 and / or the electrodes 15.

[0256] The inspection device 1 preferably includes a scale 18. The scale 18 is preferably an electronic scale 18.

[0257] The scale 18 is preferably designed to measure the weight of an animal T positioned or placed on the testing device 1 .

[0258] The test device 1 and / or the scale 18 are preferably designed for a body fat measurement, i.e. for determining the body fat percentage of the animal T on the scale 18. The body fat measurement or the determination of the body fat percentage is preferably performed via bioimpedance measurements. In particular, two or more of the electrodes 15, 15A, 15B, 15C can be used for this purpose.

[0259] The test device 1 preferably comprises a force sensor 18A. The force sensor 18A is preferably designed to measure or detect the force exerted by the animal T on the test device 1, in particular the gravitational force.

[0260] The force sensor 18A may form part of or be integral to the scale 18, but may also be provided instead of or in addition to the scale 18.

[0261] The force sensor 18A can be designed, for example, as a piezo element or a strain gauge or the like.

[0262] The testing device 1 can also comprise a number of force sensors 18A, in particular of the same kind or type. Preferably, one or more force sensors 18A are arranged below the sensor device 4, below the resting surface 3 and / or below the electrodes 15 (respectively) and / or the force sensors 18A are integrated into the sensor device 4 and / or the resting surface 3 and / or the electrodes 15. In particular, the force sensors 18A can be designed with such an arrangement to determine the presence and / or positioning of the animal T and / or to assist in such a determination.

[0263] The inspection device 1 preferably comprises a display device 19. The display device 19 is especially designed for optical display. The display device 19 is preferably formed by a display, for example an LCD display, an LED display, an OLED display or the like.

[0264] The display device 19 is preferably designed to display values ​​measured or determined by the examination device 1, such as the heart rate curve KG, the heart rate, the blood pressure BP, the body weight, the body fat percentage or the like. In particular, the display of the blood pressure BP and the heart rate curve KG by the display device 19 is shown diagrammatically in FIG.

[0265] Alternatively or additionally, the display device 19 may be designed for user guidance, for example to display instructions regarding the operation or use of the inspection apparatus 1, selection menus, error messages, warning messages or the like.

[0266] Furthermore, the inspection apparatus 1 preferably comprises an input device 20. The input device 20 is preferably designed for setting and / or adjusting and / or controlling the inspection apparatus 1. The input device 20 is preferably arranged in the immediate vicinity of the display device 19 and / or is integrated in the display device 19.

[0267] For example, the input device 20 may be formed by one or more keys, buttons, switches or the like. However, the display device 19 may be designed as a touch display or a touch-sensitive display, such that the display device 19 comprises or forms the input device 20 and / or the input device 20 is integrated into the display device 19.

[0268] The test device 1 preferably comprises a power supply device 21. The power supply device 21 is designed to supply the test device 1 with electrical energy.

[0269] Preferably, the power supply device 21 comprises an energy storage device for storing electrical energy, for example an accumulator, a battery or the like. In particular, the power supply device 21 is designed for charging an accumulator or a battery, particularly preferably for inductive charging. For this purpose, the power supply device 21 preferably comprises a corresponding charging device. Alternatively or additionally, the power supply device 21 can also comprise or form a connection for connecting the power supply device 21 to an external power source, for example a domestic power source. In particular, the connection can comprise or form a charging device or part thereof.

[0270] The inspection apparatus 1 preferably comprises a control device 25 for controlling the inspection apparatus 1 and / or the inspection. The control device 25 is preferably formed by and / or preferably comprises a processor P. The processor P is preferably a microprocessor. The control device 25 and / or the processor P are preferably designed to control the sensor devices 4, in particular the emitters 5, the detectors 6 and / or the sensors 7, to control the electrodes 15 and / or to control the scale 18.

[0271] Thus, the controller 25 is preferably coupled to the sensor device 4, the emitter 5, the detector 6, the sensor 7, the electrodes 15, the scale 18 and / or the force sensor 18A.

[0272] Furthermore, the power supply unit 21 is preferably designed to supply power to the control unit 25. In particular, the control unit 25 is coupled to the power supply unit 21.

[0273] The controller 25 is preferably designed to control and / or coupled to the display device 19. The controller 25 is preferably coupled to and / or can be operated by the input device 20.

[0274] The control device 25 is preferably designed to process and / or forward the signals measured by the sensor device 4 and / or the electrodes 15 .

[0275] The testing device 1 preferably comprises a memory and / or storage medium 26 for data storage. Preferably, the storage medium 26 is coupled to the control device 25. In particular, the storage medium 26 is designed for at least temporary storage of signals measured by the sensor device 4 and / or the electrodes 15.

[0276] Storage medium 26 may comprise and / or be formed by multiple separate components.

[0277] Preferably, storage medium 26 comprises one or more permanently attached memory modules and / or storage elements, such as a hard disk drive (HDD), solid state drive (SSD), RAM modules and / or flash memory or the like.

[0278] Alternatively or additionally, the storage medium 26 may comprise or be formed by one or more storage elements separate from and / or connectable to the test device 1, such as a USB stick or the like.

[0279] In principle, the storage medium 26 can be formed by or comprise one or more arbitrary storage devices for storing electronic data, such as a CD-ROM, a hard disk, a USB memory, a flash memory, a cloud memory, an external database, or other computing equipment separate from or external to the inspection device 1, and / or a mobile terminal device with integrated memory, such as a PC, a data center, a supercomputer, a cloud computer, a server, a mobile phone, a smartphone, a tablet, a laptop or the like.

[0280] The testing device 1 is preferably designed for the analysis and / or evaluation of signals measured by the electrodes 15, the sensor device 4 and / or the scale 18. The evaluation of the signals is preferably performed by and / or controlled by the control device 25 and / or the processor P, in particular by using a storage medium 26.

[0281] The inspection apparatus 1 preferably comprises an interface device 22 for connecting the inspection apparatus 1 with one or more external devices 23. The interface device 22 may comprise a number of, in particular different, interfaces. The interfaces may be wired or wireless interfaces. For example, the interface device may comprise one or more serial interfaces, one or more USB interfaces, one or more HDMI interfaces and / or several or more other interfaces, which are in particular designed for (in particular wired) data exchange between the external device 23 and the inspection apparatus 1. Alternatively or additionally, the interface device 22 may also comprise one or more wireless interfaces, such as a WiFi interface, a Bluetooth interface, in particular a Bluetooth Low Energy interface (BLE interface), an NFC interface or similar.

[0282] In other words, the inspection apparatus 1 is preferably designed for data exchange with an external device 23 , in particular by means of the interface device 22 .

[0283] The testing apparatus 1 is preferably designed to transmit data or signals measured by the sensor device 4 and / or the electrodes 15 and / or results or evaluations determined on the basis of these data or signals to an external device 23, in particular by means of the interface device 22.

[0284] The external device 23 is preferably a separate, in particular physically separated, device from the inspection apparatus 1 .

[0285] The external device 23 may be designed to control the test apparatus 1 and / or to record and / or evaluate and / or analyze and / or display or otherwise output the signals and / or data measured by the test apparatus 1 and / or the results transmitted by the test apparatus 1. Preferably, the external device 23 is designed to display the heart rate curve KG and / or the blood pressure BP, as shown diagrammatically in FIG.

[0286] The external device 23 is preferably designed as a mobile end device, such as, for example, a smartphone, a tablet, a laptop, and / or as a PC, a server, a computer network, a cloud, an internet portal, an app and / or another computing device.

[0287] Alternatively or additionally, the external device 23 is designed as a storage medium 26, such as a memory stick. In particular, the external device 23 may form or comprise the storage medium 26 or part thereof.

[0288] Preferably, the inspection apparatus 1 comprises an external device 23 , which forms part of the inspection apparatus 1 or which is assigned to the inspection apparatus 1 .

[0289] Preferably, the evaluation of the signals measured by the test apparatus 1, in particular by the sensor device 4 and / or the electrodes 15, 15A, 15B, 15C, is performed in or by the test apparatus 1 itself. Alternatively or additionally, the evaluation or parts thereof can also be performed outside the test apparatus 1 and / or by an external device 23.

[0290] In FIG. 8 the wiring of the electrodes 15 and the processing of the signals measured by the sensor device 4 and the electrodes 15 are shown in a schematic representation in the form of a block diagram.

[0291] The inspection device 1 preferably has a preprocessing device 27. The preprocessing device 27 preferably has, or is formed by, an amplifier, particularly a differential amplifier. The differential amplifier is particularly preferably formed by, or has, an operational amplifier. However, other solutions are also possible.

[0292] The preprocessing device 27 is preferably coupled or connected to the electrode 15 and is particularly designed to preprocess the signals measured by the electrodes 15, 15A, 15B, 15C. In particular, the preprocessing device 27 amplifies the difference between the signals measured at different electrodes 15, particularly the voltage such as the bioelectric potential, and is particularly preferably designed to amplify the difference between the signal measured at the first electrode 15A and the signal measured at the second electrode 15B.

[0293] Optionally, the electrode 15 is coupled to the preprocessing device 27 via a capacitance or a capacitor. This is shown by the capacitance symbol within the dotted box in FIG. 8.

[0294] Furthermore, the preprocessing device 27 is preferably designed to filter the signals measured by the electrode 15.

[0295] Preferably, although merely optionally, the preprocessing device 27 has a common-mode rejection device 28.

[0296] The common-mode rejection device 28 is preferably designed to suppress or filter the DC current component or the DC voltage component of the signals measured by the various electrodes 15.

[0297] The inspection device 1 preferably has an A / D converter 29. The A / D converter 29 is preferably designed to convert the signals preprocessed by the electrode 15 and, in some cases, by the preprocessing device 27, particularly analog signals, into digital signals. The A / D converter 29 is preferably downstream of the preprocessing device 27.

[0298] The signals measured at the electrodes 15, in particular the heart rate curve KG recorded at the electrodes 15, are preferably further evaluated and / or processed, in particular after conversion to a digital signal. In particular, a usability check can be performed, for example, by the checking device 29A. During the usability check, it is preferably determined whether the heart rate curve KG is useful, i.e. can be meaningfully evaluated and / or contains useful information. This is diagrammatically indicated by the box in the lower right corner in FIG. 8.

[0299] Preferably, the inspection apparatus 1 comprises, as an alternative or in addition to the pre-processing device 27, one or more further pre-processing devices 30. The pre-processing devices 30 are preferably designed for pre-processing of the signals S measured by the sensor device 4 or the detector 6 and / or the sensor 7.

[0300] The pre-processing device 30 preferably comprises an amplifier 31. The amplifier 31 is preferably designed to amplify the signal S measured by the detector 6 or sensor 7. In particular, the amplifier 31 is a transimpedance amplifier and / or converts a current into a voltage.

[0301] Preferably, the pre-processing device 30 comprises a filter device 32 for filtering the signal S, which is notably amplified by the amplifier 31 .

[0302] The filter device 32 preferably comprises a number of different electrical filters. In particular, the filter device 32 may comprise or form one or more passive filters and / or one or more active filters. The filter device 32 may for example comprise or form one or more bandpass filters, bandstop filters, highpass filters and / or lowpass filters.

[0303] Preferably, each detector 6 or sensor 7 is assigned or comprises a pre-processing device 30 .

[0304] Preferably, the evaluation of the signal S measured by the sensor device 4 and preferably preprocessed by the preprocessing device 30, in particular the curve K, is carried out together with and / or taking into account the heart rate curve KG.

[0305] The results of the evaluation can then be transferred to an external device 23, for example as already mentioned above and illustrated diagrammatically in FIG.

[0306] The inspection device 1 is preferably designed to carry out the method described below. Alternatively or additionally, the inspection device 1 can be used to carry out the method described below. This use can also be realized independently of further aspects of the invention.

[0307] The method according to the present invention will now be described in detail.

[0308] The method is preferably carried out using the above-mentioned inspection device 1. The above-mentioned inspection device 1 is particularly advantageous for carrying out the method, in particular for the selection of one or more sensors 7 and / or for the evaluation of one or more curves K. However, the method can also be carried out independently of the described inspection device 1, preferably with an inspection device 1 designed differently from the one described above.

[0309] The inspection device 1 is preferably designed to carry out the method described below. Alternatively or additionally, the inspection device 1 can be used to carry out the method described below. This use can also be realized independently of further aspects of the invention.

[0310] In particular, the inspection device 1 comprises means for carrying out the steps of the method. These means preferably comprise or are formed by a computer program.

[0311] The means and / or computer program preferably comprise instructions which, when executed, cause the inspection device 1 to carry out the described method.

[0312] According to another aspect, the computer program and / or instructions are stored on the computer readable storage medium 26 or the computer readable storage medium 26 includes the computer program and / or instructions.

[0313] For a medical examination with the examination device 1, in particular for blood pressure measurement, it is preferably intended to place an animal T, in particular a domestic cat or a domestic dog, on the examination device 1. In particular, the animal T is placed completely on the examination device 1, i.e. preferably such that all limbs, in particular the legs 2, are on the examination device 1 and / or such that the entire body weight of the animal T is supported by the examination device 1.

[0314] Particularly preferably, the animal T is positioned on the testing apparatus 1 such that the leg 2 of the animal T, in particular the front leg, rests on the sensor device 4 and / or is located directly above the sensor device 4, and / or a curve K containing information about the arterial blood flow BF can be recorded for the leg 2.

[0315] Preferably, the animal T is positioned such that each of the electrodes 15, 15A, 15B, 15C contacts a body part of the animal T, in particular the leg 2, so that the heart rate curve KG can be recorded by the electrode 15. In particular, the animal T is positioned such that one of its front legs contacts the first electrode 15A, the other leg contacts the second electrode 15B, and, if the testing device 1 has a third electrode 15C, one or both of its rear legs contact the third electrode 15C.

[0316] After positioning the animal T, the medical examination and / or blood pressure measurement is preferably started. Optionally, after positioning the animal T, it is possible to first wait a short time to allow the animal T to settle down, and only after the waiting time the medical examination and / or blood pressure measurement is started. In particular, a curve K is recorded for the medical examination or blood pressure measurement, which curve K is in particular a photoplethysmogram.

[0317] In the lower part of FIG. 9, a curve K is shown as an example.

[0318] Particularly preferably, a reflectance measurement is performed or the testing device 1 is designed for this purpose in order to record the curve K. This means in particular that the sensor device 4 is arranged only on one side of the leg 2 and / or does not have any components arranged on the opposite side of the leg 2.

[0319] Preferably, the inspection or measurement is carried out using radiation R in the infrared range.

[0320] It is particularly preferred that the examination device 1 records a heart rate curve KG of the animal T, in particular at the same time as recording the curve K which contains information about the arterial blood flow BF of the animal T.

[0321] The upper part of FIG. 9 shows a heart rate curve KG as an example.

[0322] The inspection device 1 may comprise a processor P which receives and / or processes information and / or signals S and / or curves K from the inspection device 1, in particular the sensor device 4, the sensor 7, the detector 6 and / or the electrodes 15. Alternatively or additionally, the processor P and / or the inspection device 1 may comprise a storage medium 26 which comprises a computer program representing the proposed method, which program may be executed by the processor P to carry out the method. In particular, the computer program is stored on the storage medium 26. Furthermore, results may be formed in the processor P. These results may be output in particular via a display device 19 and / or transmitted in particular to an external device 23.

[0323] The storage medium 26 can be a storage means that is integrated into the inspection device 1 or that is separate, e.g. a memory stick or an external database, server or the like, that can be connected to the inspection device 1 via an interface. The computer program can also be supplied to the inspection device 1 from the outside and stored therein. However, other solutions are also possible here.

[0324] The method, in particular the optical inspection, is preferably carried out with at least one sensor 7, preferably with a plurality of sensors 7. Preferably, each sensor 7 corresponds to one measurement channel, each sensor 7 corresponds to one measurement channel and / or one measurement channel is assigned to each sensor 7.

[0325] A "measurement channel" in the sense of the present invention is preferably a transmission path of a signal S measured by a sensor 7, in particular a curve K measured by a sensor 7. In this sense, the terms "measurement channel" and "sensor" are closely connected to each other, so that in the following no distinction is made between sensor 7 and measurement channel. Instead, in the following the terms "measurement channel" and "sensor" are used synonymously, and the term "sensor" will be predominantly used. In particular, the terms "measurement channel" and "sensor" are interchangeable.

[0326] A number of curves K can be recorded via a number of sensors 7, preferably separately or independently of one another, simultaneously and / or one after the other.

[0327] Preferably, each sensor 7 has at least one detector 6. Very particularly preferably, each sensor 7 has exactly one detector 6. Thus, by selecting a sensor 7, the detector 6 is also selected and vice versa. In this respect, the terms "sensor selection" and "detector selection" are preferably synonymous and in particular interchangeable.

[0328] Furthermore, as already mentioned above, each sensor 7 preferably has a sensor area 11. In other words, each sensor 7 is preferably assigned to a different measurement location or partial area of ​​the sensing area 12 of the sensor device 4. In particular, each sensor 7 corresponds to a certain measurement location and / or sensor area 11 and / or partial area of ​​the sensing area 12. Selection of a sensor 7 can therefore be understood as selection of a measurement location and / or sensor area 11 and / or partial area of ​​the sensing area 12. The terms "selection of a sensor", "selection of a measurement location", "selection of a sensor area" and "selection of a partial area of ​​the sensing area" are therefore preferably synonymous with each other and in particular interchangeable.

[0329] Furthermore, one or more curves K are preferably recorded for each sensor 7. In other words, each curve K is assigned to a sensor 7. In particular, each curve K corresponds to a certain sensor. The selection of the curve K can therefore be understood as and / or represents a selection of the sensor 7. Indirectly, the selection of the curve K also represents a selection of the measurement location and / or of a sub-area of ​​the sensor area 11 and / or of the sensing area 12. The terms "selection of the curve", "selection of the measurement location", "selection of the sensor area", "selection of a sub-area of ​​the sensing area" are preferably synonymous with each other and in particular interchangeable.

[0330] Furthermore, in the above-described inspection device 1, the sensors 7 are preferably of the same kind or type, so that each sensor 7 performs in principle the same measurement, the measurements differing only in that they are measured at different positions, resulting in different (simultaneous) measurement signals S or curves K.

[0331] FIG. 10 shows a schematic diagram of the general sequence of the method.

[0332] The method preferably comprises a number of steps S1 to S9, which are shown diagrammatically in Fig. 10. In the following, first a rough outline of steps S1 to S9 will be given, followed by a more detailed description of steps S1 to S9.

[0333] The method according to the invention does not necessarily include all steps S1 to S9. In particular, the individual steps S1 to S9 or individual aspects of steps S1 to S9 may be feasible independently of one another or in different combinations.

[0334] In the method according to the invention, an animal T is medically examined. Preferably, the pulse transit time PTT and / or the blood pressure BP of the animal T are determined in the method according to the invention.

[0335] An animal T is preferably placed for testing on the testing apparatus 1. Preferably, the animal T is not fixed on the testing apparatus 1 and can move freely, in particular relative to the sensor device 4 and / or the electrodes 15.

[0336] In step S1, it is preferably determined whether the animal T is located on the testing device 1 and / or whether it is positioned on the testing device 1 such that a medical test can be performed by the testing device 1. However, step S1 is only optional and may be omitted.

[0337] In step S2 it is preferably determined whether the leg 2 is positioned on or above the sensor device 4 so that an optical examination, in particular photoplethysmography, can be performed with the sensor device 4. Alternatively or additionally, in step S2 it is determined on which sensor 7 the leg 2 is positioned or by which means of the sensor 7 the examination can be performed. Preferably, only the sensor 7 on which the leg 2 is positioned and / or on which the examination can be performed is selected and / or used. Step S2 can also be performed simultaneously with step S1 or can replace it. Step S2 is optional and can also be omitted.

[0338] Preferably, the selection of the sensor 7 or a subset of the sensors 7 for which the inspection is to be carried out is made in step S3. This is particularly advantageous when the sensor device 4 has a plurality or a large number of sensors 7. In this way, in particular, by excluding and / or not selecting the sensors 7 and / or detectors 6 where the legs 2 are not arranged from the measurement or evaluation, the labor required for the measurement and / or evaluation can be significantly reduced. Step S3 can also be executed simultaneously with step S1 and / or step S2. However, step S3 is in principle optional and can also be omitted.

[0339] On the other hand, the selection of step S3 or the sensor 7 or a subset of the sensors 7 can be advantageous even without subsequent steps, and in particular, the present invention can be formed without subsequent steps.

[0340] In step S4, a curve K containing information on the arterial blood flow BF of the animal T, in particular a photoplethysmogram, is recorded. Preferably, it is preferable to record the cardiac curve KG, in particular simultaneously with recording the curve K.

[0341] In particular, it is preferable to record a plurality of curves K simultaneously, in particular simultaneously with the cardiac curve KG. Alternatively or additionally, a plurality of curves K and / or the cardiac curve KG can be recorded one after another, in particular with a time interval. In step S4, preferably, the quality of the measurement and / or the usefulness of the recorded curve K and / or the cardiac curve KG are also checked.

[0342] In step S5, the curve K containing information on the arterial blood flow BF is preferably segmented or divided into curve sections KA. This is done in such a way that the curve sections KA correspond to the heartbeats, in particular preferably in such a way that each curve section KA corresponds exactly to one heartbeat. Preferably, the curve K is segmented into the curve sections KA using the information from the cardiac curve KG. However, other solutions are also possible here.

[0343] In step S6, a selection of the curve section KA is preferably made for further evaluation, in particular for the determination of the curve characteristic M and / or the blood pressure BP. For this purpose, in step S6, a part of the curve section KA can be discarded. The selection of the curve section KA preferably constitutes the selection of one or more sensors 7, in particular if only the curve section KA is selected from a single sensor 7 or a subset of sensors 7. However, step S6 is optional and can also be omitted.

[0344] In step S7, an averaging or averaging determination based on the curve section K A is preferably performed. Preferably, one or more curve mean values ​​K M are determined based on the curve section K A. Preferably, a bootstrap method is used or applied.

[0345] In step S8, preferably, a curve feature M is determined. For this purpose, preferably, first a plurality of curve features M are determined. In particular, a curve feature M is determined separately for each sensor 7, for each curve section KA and / or for each curve mean value KM. Particularly preferably, in addition to each curve feature M, an assigned degree of dispersion is determined in each case. Particularly preferably, as a final result of the curve features M determined in step S8, the curve feature M having the lowest degree of dispersion is selected. This selected curve feature M then represents the curve feature M determined in step S8. The determined curve feature M can then be output and / or used as a basis for blood pressure BP measurement.

[0346] In step S9, preferably the blood pressure BP is determined, in particular from the curve characteristic M determined in step S8. This is done in particular by means of a correlation function F, which is preferably empirically determined.

[0347] During one or more of steps S5, S6, S7 and / or S8, a check can be made in particular as to the usefulness of the heart rate curve KG and / or the curve K.

[0348] The check on the usefulness of the heart rate curve KG is preferably carried out immediately after the start of the examination or recording of the heart rate curve KG, in particular after a few seconds, preferably after a maximum of about 5 seconds, particularly preferably after about 2 seconds.

[0349] The check of the usefulness of the curve K is preferably carried out after checking the usefulness of the heart rate curve KG, in particular after at least about 5 seconds and / or at most about 45 seconds, particularly preferably after about 10 seconds and / or after about 30 seconds. In particular, the check of the usefulness of the curve K is particularly preferably carried out several times and / or after two different times, in particular a first check after about 10 seconds and a second check after about 30 seconds.

[0350] The (first and / or second) check of the usefulness of the curve K is preferably performed during or in parallel with the recording of the curve K.

[0351] If the measurements are determined to be not useful and / or further measurements are required, then after these steps S5, S6, S7 and / or S8, one can return to step S4, as indicated by the arrows in FIG. 10, and / or new and / or additional measurements can be made.

[0352] Alternatively or additionally, it is also possible to return to step S3 after one of steps S4, S5, S6, S7 and / or S8 and / or to make a new and / or different selection of sensors 7.

[0353] After returning to step S3 or step S4, it is preferable to execute the following steps S4 to S9 or S5 to S9 again, either completely or partially.

[0354] By returning to the previous step and executing one or more steps multiple times and / or again, even if animal T moves during the examination or leg 2 moves during the examination, the examination of animal T, particularly the measurement of blood pressure BP, can be accurately and reliably performed. In particular, by repeating one or more steps, it becomes possible to perform cumulative measurements or recordings until a sufficient number of data or curve K becomes measurable or available. Thereby, measurement errors and / or motion artifacts can be compensated, and movement of animal T or leg 2 during the examination becomes possible. Since animal T can preferably move freely during the examination, the examination is very comfortable for animal T and thus stress-free. This contributes to an accurate and reliable examination, particularly blood pressure measurement.

[0355] Hereinafter, steps S1 to S9 will be described in more detail.

[0356] Step S1 Preferably, in step S1, the presence of animal T on the examination device 1 is determined.

[0357] The examination device 1 is preferably designed to identify the (potential) presence of at least one of the electrodes 15 and / or animal T, particularly leg 2, on or in the examination device 1, particularly on the placement surface 3 and / or on the sensor device 4.

[0358] In principle, for this purpose, different methods can be used and / or different sensors can be provided. For example, the examination device 1 can have a presence sensor such as a light barrier, a motion detector or the like (not shown). However, it is particularly preferred to use one or more components of the examination instrument 1, particularly a sensor including an electrode that also serves another purpose.

[0359] Most particularly preferably, one or more of the sensor device 4, or the sensors 7 and / or the detectors 6, the force sensors 18A and / or one or more of the electrodes 15 are used to detect the presence of animal T or leg 2 on the examination device 1 and / or on the sensor device 4.

[0360] Particularly preferably, the test device 1 identifies the contact of the leg 2 with one or more of the electrodes 15, in particular by measuring the impedance or resistance between the electrodes 15. The resistance measured at the electrodes 15 varies in particular depending on whether the electrodes 15 are in contact with the leg 2 of the animal T or not. In this way, the presence of the animal T and / or the correct positioning of the leg 2 on the electrodes 15 can be identified, in particular the positioning of the leg 2 such that the heart rate curve KG can be recorded by the electrodes 15.

[0361] Alternatively or additionally, the force sensor 18A and / or the scale 18 can be used to identify the presence of this animal T. In particular, a force or weight threshold can be specified or specifiable for this purpose. In this case, the force or weight threshold is preferably selected such that it is exceeded when the domestic cat or dog or other animal T to be tested is placed on the testing device 1. Exceeding the weight threshold is therefore indicative of the presence of the animal T. Falling below the weight threshold is indicative of the animal T not being positioned on the testing device 1 and / or that the animal T is only partially positioned on the testing device 1 or is not positioned on the testing device 1 in the intended manner.

[0362] By suitable positioning of the force sensor 18A, it is preferably also possible for the force sensor 18A to determine whether and / or which electrode 15 and / or sensor device(s) 4 the animal T is in contact with.

[0363] Alternatively or additionally, one or more of the sensor device 4 or the sensor 7 and / or the detector 6 can be used to identify or determine the presence of the animal T. In particular, it can be determined by the sensor device whether the leg 2 or other body part of the animal T is located directly above the sensor device 4 and / or is positioned so that the leg 2 and / or body part can be optically inspected by the sensor device 4, in particular whether photoplethysmography can be performed. This is preferably done by comparing the signals S measured by the sensors 7 of the sensor device 4.

[0364] In this connection, on the one hand, it can be exploited that the radiation R emitted by one or more of the emitters 5 reaches one of the detectors 6 at least essentially only in the presence of an object, i.e. preferably an animal T, in particular by reflection or scattering. On the other hand, it can be exploited that, due to the legs 2 arranged on the sensor device 4, the ambient light is at least partially blocked and / or reaches only some of the sensors 7. Information about the presence of an animal T can thus be gleaned from the signal S measured by the respective detector 6 or sensor 7, without the need to particularly evaluate the signal S in detail. For example, it is sufficient to identify a certain signal S by comparing the signal level, for example with a threshold value or by comparing it with signals S measured by other sensors 7 or the like.

[0365] The presence detection or presence determination can be performed continuously, but is preferably performed intermittently for energy efficiency.

[0366] The result of the presence detection or presence determination is preferably stored. The result is preferably binary information, since either the animal T is present or its presence can be determined (positive result) or the animal T is not present or its presence cannot be determined (negative result). In particular, the result or information is coded in the signal for one or more of the sensors 7 and / or detectors 6 and / or electrodes 15, in particular in bits, most preferably in the least significant bits. Such a method is also known as "lead-off detection".

[0367] Preferably, the presence detection or presence determination is performed automatically, continuously and / or repeatedly and / or (again) at regular intervals, for example at intervals of less than 2 seconds or less than 1 second, during the examination and / or recording of the curve K and / or the heart rate curve KG.

[0368] If it is determined that an animal T or its leg 2 is (probably) present on the inspection device 1, the inspection device 1 can be (automatically) switched on, in particular switched from a power-saving mode to an operational mode. The inspection device 1 can therefore be designed to support a power-saving mode and to leave this power-saving mode as soon as the presence of an animal T or its leg 2 is detected.

[0369] Determining the presence of the animal T or leg 2, and in particular controlling the power supply of the inspection device 1 thereby, is advantageous, but in principle, especially for the further steps of the invention, starting up the inspection device 1, although less convenient, is not essential, in particular since this can be done alternatively or additionally by a switch or other operating device of the inspection device 1.

[0370] Step S2 Preferably, in step S2 the inspection device 1 checks whether and / or in what position the leg 2 is on the sensor device 4 or whether the inspection device 1 is designed specifically for this purpose with the sensor device 4.

[0371] To enable the proposed test, the leg 2 of the animal T must be on or in contact with the sensor device so that an optical test as described above can be carried out. Particularly preferably, the leg 2 rests directly on the sensor device 4, in particular on the cover 14 for this purpose. In this case, a reliable optical test can be carried out. Alternatively or additionally, the leg 2 of the animal T must be in direct electrical or galvanic or possibly capacitive contact with the electrode 15, so that a recording of the heart rate curve KG can be reliably carried out.

[0372] In step S2 it is preferably checked automatically whether the leg 2 is resting on the sensor device 4 or is in contact with it in an appropriate manner, allowing an examination, in particular an optical examination and / or recording of the heart rate curve KG.

[0373] On the one hand, the signal S measured by the sensor 7 can be evaluated. This can consist simply in determining whether one or more signals S correspond to the incidence of light. In this way, the shadow cast by the animal T or by the leg 2 can be determined and thus the position of the leg 2 on the sensor device 4 can be detected.

[0374] It is particularly advantageous to measure the electromagnetic radiation R emitted by the emitter 5 by means of the detector 6. When the emitter 5 is activated, by evaluating one or more signals S from the detector 6, it is also possible to determine whether the object, and in particular the leg 2 of the animal T, is positioned in such a way that the radiation R emitted by the emitter 5 reaches the detector 6. In this case, or depending on its intensity, the presence of the leg 2 on the sensor device 4 can be deduced.

[0375] Determining the presence and / or position of the leg 2 above the sensor device 4 is preferably done by comparing the signals S measured by the sensors 7 of the sensor device 4 .

[0376] The comparison of the signals S measured by the sensors 7 and / or detectors 6 is preferably carried out with the emitters 5 activated or switched on or emitting, but can also be carried out with the emitters 5 switched off.

[0377] By comparing the signals S from the different sensors 7 and / or detectors 6 it can preferably be determined in which position the leg 2 is in particular relative to the sensor device 4 and / or the different sensors 7 and / or detectors 6. In particular it can be determined on which of the sensors 7 and / or detectors 6 of the sensor device the leg 2 is located and thus by which sensor 7 and / or detector 6 an examination, in particular a measurement of the blood pressure BP, can be performed. In particular the shape and / or positioning of the leg 2 can preferably be modelled.

[0378] When the leg 2 is located on the sensor device 4, preferably some areas and / or some sensors 7 of the sensor device 4 are covered by the leg 2, while other areas and / or sensors 7 are not covered by the leg 2. In particular, this results in differences in the brightness and / or radiation R measured by the individual sensors 7. For inspection by the sensor device 4, it is preferably intended that the leg 2 is positioned on the sensor device 4 such that the sensor 7 or at least one sensor 7 is completely covered by the leg 2. In this way, ambient light cannot reach the sensor 7 or its detector 6, and only radiation R emitted by the emitter 5 or one of the emitters 5 of the sensor 7 and scattered in the leg 2 towards the detector 6 can reach.

[0379] The comparison of different sensors 7 and / or signals S measured by the sensors 7 is preferably performed by forming a difference between the signals S of the different sensors 7 .

[0380] Alternatively or additionally, the determination of the location or presence by the sensor device 4 can be performed by checking whether the signal S measured by the sensor device 4 exceeds or falls below a threshold value, in particular an absolute signal strength.

[0381] Preferably, the threshold value represents an absolute brightness. In this way, it is possible to determine in particular whether the leg 2 and / or any other body part of the animal T is located above a sensor 7 of the sensor device 4 and / or which sensor 7 of the sensor device 4 the leg 2 or any other body part is located above.

[0382] In particular, exceeding the threshold indicates that no part of the animal T's body is over the sensor device 4 or sensor 7, and / or falling below the threshold indicates that the leg 2 or another part of the animal T's body is located over the sensor device 4 and / or sensor 7 so that the curve K can be recorded.

[0383] Alternatively or additionally, it may be provided that the wavelength of the radiation R measured by the detector 6 or the sensor 7 is analyzed. Preferably, the emitter 5 is designed to emit radiation R at a certain wavelength or a narrow wavelength range. In other words, the emitter 5 preferably has a narrow spectrum. In contrast, ambient light such as sunlight and / or artificially generated light for room lighting usually has a broad spectrum, i.e. several different wavelengths, which are outside the wavelength range emitted in particular by the emitter 5. Thus, by spectral analysis of the radiation R detected by the detector 6 or the sensor 7, it may preferably be determined whether the sensor 7 is covered by the leg 2 or whether ambient light is measured.

[0384] If it is determined that the leg 2 is located only over some of the sensors 7 of the sensor device 4, and in particular not over all of the sensors 7 of the sensor device 4, then these sensors 7 can be selected for performing an examination and / or for recording a curve K containing information about the arterial blood flow BF.

[0385] For the presence and / or position determination by the sensor device 4, in particular a scan or search can be carried out by the sensor 7, in which different sensors 7 and / or emitters 5 are activated or switched on one after the other. In particular the influence of ambient light can be determined in this way and / or by comparing a signal S measured with the emitter 5 switched on and a signal S measured with the emitter 5 switched off.

[0386] To determine the position of the leg 2 above and / or relative to the sensor device 4, in particular the centre of mass or centre of gravity of the signal S measured by the sensor 7 and / or detector 6 is calculated or determined. The signal S is preferably proportional to the intensity of the radiation R measured by the respective sensor 7 and / or detector 6.

[0387] The determination of the centre of mass or centre of gravity of the measured signal S is carried out in particular as follows.

[0388] First, preferably, each emitter 5, detector 6 and / or sensor 7 is assigned a position, preferably represented by two coordinates x, y. Thus, the position of each emitter 5, detector 6 and / or sensor 7 is represented by the coordinates (x i、 y i ), where the index i counts the number of emitters 5, detectors 6 and / or sensors 7. This is also shown in particular in FIG.

[0389] The position of leg 2 or the center of mass or gravity of signal S is given by the following coordinate pair (x c ,y c ) is given by

number

number

[0390] Here, S i are the respective coordinates x iOr y i The signal strength S of the signal S measured at orig,i , or the respective coordinate x i Or y i The signal strength S measured at orig,i The coefficient 1 / S is the sum of the tot is a normalization factor and can be omitted if desired. Preferably

number

[0391] Signal Strength S orig is preferably the value of the signal S measured by the sensor 7 and / or detector 6, e.g. a voltage, current or the like, in particular a DC value measured by the sensor 7 and / or detector 6.

[0392] Signal Strength S orig,i The value S corresponding to i is the signal strength S orig,i A value that is directly linked to the signal strength S orig,i Its own value (S i =S orig,i ) is preferred. Particularly preferred is the value S i is the signal strength S orig,i and signal strength S i The mean or median of S m Difference with (S i =S orig,i -S m ) or its absolute value (S i =|S orig,i -S m |).

[0393] Position of leg 2 or center of mass or center of gravity (x c ,y cAfter the determination of (), one or preferably a plurality of sensors 7, emitters 5 and / or detectors 6 are preferably selected or used based on the determined position or the determined center of gravity, particularly for medical examinations, especially photoplethysmography. Preferably, the sensor 7, emitter 5 and / or detector 6 that is closest to the determined position and / or is at a certain position around the determined position is selected or used. For example, sensors 7, emitters 5 and / or detectors 6 located in a square, rectangle, (regular) hexagon, (regular) octagon or the like around the center of mass or gravity (x c , y c ) are selected.

[0394] During and / or in one or more of the subsequent steps of the optical inspection, particularly between one of steps S3 and / or S4, it is preferable to check whether the position of the leg 2 has changed, particularly during the measurement and / or after the initial positioning, and / or to repeat the determination of the position of the leg 2. This position check is preferably performed automatically, continuously, and / or at regular intervals, preferably at intervals of less than 2 seconds or less than 1 second.

[0395] To check whether the position of the leg 2 has changed after the initial positioning, the signal S measured by the sensor 7, emitter 5 and / or detector 6, particularly those selected or used for the inspection, or the control value S determined from these signals S new is compared with the reference value S ref .

[0396] The reference value S ref is preferably the value measured and / or determined during the initial determination of the position of the leg 2 prior to the check and is preferably stored.

[0397] The control value S new is preferably determined based on the signal S measured using the same method as the reference value S ref and / or using the same sensors 7, emitters 5 and / or detectors 6 used to determine the reference value S ref for the signals S. In other words, the control value Snew and the reference value S ref The only difference between these is that they are recorded or determined at different times, i.e. at the initial determination of the position of leg 2 or at the reference value S before the medical examination. ref and a control value S after an initial determination of the position of the leg 2 or during a medical examination, in particular photoplethysmography. new It is.

[0398] Preferably, the reference value is the signal S or signal strength S measured by the selected sensor 7, emitter 5 and / or detector 6. orig The value S is determined based on ref Particularly preferably, the reference value S ref is the value S of the (selected) sensor 7, emitter 5 and / or detector 6 i Sum of (

number

number

[0399] Control value S new and the reference value S ref When comparing with the control value S new The standard value S ref Deviation from control value S new and the reference value S ref Ratio to control value S new and the reference value S ref or the like is determined or calculated.

[0400] Particularly preferably, the control value S new and the reference value S ref Withnew / S ref By determining the control value S new is the standard value S ref is compared to.

[0401] More preferably, to obtain the result of the comparison, the value determined in the comparison, e.g. the control value S new and the reference value S ref The difference between the quotient S new / S ref is checked to see if it is greater than or equal to a specified or specifiable threshold.

[0402] Control value S new and the reference value S ref The result of the comparison with is preferably either that the position of the leg 2 has changed or that the position of the leg 2 has not changed.

[0403] The value determined in the comparison, in particular the quotient S new / S ref If is greater than or equal to a specified threshold, the result of the comparison is preferably that there is no change in the position of leg 2. The threshold may be, for example, 0.5.

[0404] Control value S new and the reference value S ref If the result of the comparison with is that the position of leg 2 has changed (from its originally determined position), then the position of leg 2 is preferably determined again, in particular by the method described above.

[0405] Control value S new and the reference value S ref The comparison with is preferably performed at regular (time) intervals, for example every 1 second, every 2 seconds, every 3 seconds or the like.

[0406] If it is found that the position of leg 2 has changed, and / or the reference value S ref and the control value S new If the value determined in the comparison with is equal to or greater than the threshold value, then the determination of the position of the leg 2, in particular the search run or scan, is preferably carried out again, in particular automatically.

[0407] As an alternative or in addition to a presence and / or position determination by the sensor device, one or more of the electrodes 15 can be used to detect the presence of the leg 2 on the sensor device 4. In this case, a measurement is preferably performed to determine whether there is a conductive, in particular direct (galvanic) or capacitive, electrical connection between the leg 2 and the electrode 15 assigned to the sensor device 4 or whether it is located as part of or on the sensor device. If an electrical connection is present, this indicates the presence of the leg 2.

[0408] These measures can be combined in a particularly advantageous way: in particular, the sufficient presence of the leg 2 is automatically detected if both a contact with the electrode 15 and an occlusion of one or more detectors 6 or an identification of the detector 6 of the electromagnetic radiation coming from the emitter 5 are registered.

[0409] Presence detection is preferably performed in an energy-saving manner. For example, the presence detection of the leg 2 on the sensor device 4 can be performed in several steps.

[0410] The means can be stacked on top of one another, for example a particularly intermittent and / or energy-saving means can be used first and, if a (potential) presence of an animal T is detected, this can be verified by one or more of the other means.

[0411] In a first step, the emitter 5 can be deactivated to save power. Then, if shadowing is detected at the detector 6 and / or electrical contact is detected at the electrode 15, it can be verified in a further step by other means as mentioned above and / or by activating the emitter 5 that the leg 2 is resting on or lying against the sensor device 4 so that the test can be performed.

[0412] In principle it is therefore particularly preferred to use the devices provided by the inspection device 1 for carrying out the inspection in addition to the presence determination of the leg 2 on the sensor device 4 .

[0413] Preferably, the further steps of the method are only executed if the presence of a leg 2 on or at the sensor device 4 is identified. Otherwise, energy and computing power would be expected to be expended without any meaningful results being expected.

[0414] However, in principle, the proposed method can also be carried out without step S2, in particular if the additional effort of accepting the evaluation of signals that may not have corresponding information in certain cases is acceptable and / or if, based on the evaluation at a later point in the proposed method, suitable signals S or parts thereof are selected and / or unsuitable ones are discarded.

[0415] In principle, step S1 can be complemented or replaced by step S2, due to the fact that the identification or detection of the presence of the leg 2 on the sensor device 4 is preferably concomitant with the detection of the animal T on the test device 1. This means that the evaluation of one or more signals S from one or more detectors 6 and / or the use of one or more electrodes 15 of the test device 1 for determining the electrical contact with the leg 2 can also be used to determine the presence of the animal T on the test device 1.

[0416] Step S2, in particular the determination of the position of the leg 2 above the sensor device 4 and / or checking whether the position of the leg 2 has changed, can also be carried out multiple times and / or simultaneously with the measurement or recording of the heart rate curve KG and / or one or more curves K and / or simultaneously with the evaluation of the measured or recorded values. Particularly preferably, it is checked automatically, continuously or periodically and / or at short intervals, for example at intervals of 2 seconds or less than 1 second, whether the leg 2 has been moved. In particular, step S2 can thus be carried out simultaneously with one or more of steps S4, S5, S6, S7, S8 and / or S9.

[0417] In particular, this allows the examined animal T to move during the examination and / or the leg 2 to move during the examination. Measurement errors and / or movement artifacts resulting therefrom can be compensated for by the position determination, in particular in connection with the selection of the sensor 7 and / or with the discarding of unusable curves K or curve sections KA. In particular, during and / or after the movement of the animal T or the leg 2, it is possible for the examination to be continued or continued with one or more other sensors 7 or a different subset of sensors 7 than before the movement. The fact that the animal T can preferably move freely during the examination makes the examination very comfortable and stress-free for the animal T. This results in accurate and reliable examinations, in particular blood pressure measurement examinations.

[0418] Step S3 Very particularly preferably, the detector 6 and / or the sensor 7 are selected. In particular, the selection of the detector 6 or the selection of the signal S measured by the sensor 7 also represents or constitutes the selection of the sensor 7, or vice versa. In particular, the pre-selection of the sensor 7 is performed in such a way that further steps, in particular the evaluation of the signal S measured by the sensor 7, are performed if information and / or assessability for the determination of the curve characteristic M and / or the measurement of the blood pressure BP is expected.

[0419] The selection of the sensor 7 is thus effected in particular in that a measurement is performed with this sensor 7 and in particular a signal S and / or a curve K are recorded and in particular supplied for further evaluation. Alternatively or additionally, the selection of the sensor 7 can also be effected by activating and / or switching on the emitter 5 of the sensor 7 and / or in that the measured signal S is recorded.

[0420] The non-selection of a sensor 7 is effected in particular in that no signal S is measured at the sensor 7 and / or no curve K is recorded and / or the signal S measured at the sensor 7 or the recorded curve K is not taken into account in the further evaluation. In particular, the signal S from the non-selected sensor 7 is thus rejected.

[0421] The selection of detectors 6 and / or sensors 7 is shown diagrammatically in Figure 11, where a cross represents that the respective detector 6 or sensor 7 is not selected and a hook represents that the respective detector 6 or sensor 7 is selected. In the example of step S3, two of the six detectors 6 and / or sensors 7 shown are selected and four detectors 6 and / or sensors 7 are not selected.

[0422] In this connection, it should be taken into account that in order to carry out an optical examination, and in particular photoplethysmography, a part of the leg 2 having at least one artery A must be arranged in the sensor area 11 of the sensor 7, so that an optical examination and in particular photoplethysmography can be carried out. This is shown diagrammatically in FIG. 7.

[0423] For carrying out an optical examination, in particular photoplethysmography. Thus, a body part, in particular the leg 2, is preferably placed on the sensor device 4 and / or on the cover 14, such that the arterial blood flow BF is examined by the sensor device 4 and / or the signal S contains information about the arterial blood flow BF. In other words, the body part, in particular the leg 2, is particularly positioned such that the signal S contains information about the arterial blood flow BF.

[0424] In order to carry out an optical test, in particular photoplethysmography, it is particularly preferred that the ball / paw of the leg 2 is placed on / against the sensor device 4 and / or the cover 14. In particular, the hairless area on the underside of the leg 2 is referred to as the paw. It has been shown that optical tests can be carried out particularly well in the area of ​​the paw. It has also been shown that optical tests and photoplethysmography are difficult to carry out on the outside of the paw due to the presence of hair.

[0425] It is therefore preferably detected or determined which of the sensors 7 and / or detectors 6 are located under the leg 2, in particular under the pad, and thus particularly suitable for carrying out an optical examination. Preferably, these detectors 6 and / or sensors 7 or the signals S measured with them are selected. In this way, the further evaluation can be limited to the signals S or sensors 7, respectively, which potentially lead to a curve K which indicates useful or assessable information about the arterial blood flow, and / or on the basis of which a photoplethysmography can be carried out, in particular a measurement of the pulse wave transit time PTT and / or the blood pressure BP. This allows the examination to be carried out in a particularly energy-saving manner.

[0426] Selection of the signal S and / or the sensor 7 preferably at least indirectly results in the selection of a part of the sensor device 4, a subset of the sensor 7 and / or the detector 6 and / or a subset of the sensing area 12 or the sensor area 11 and / or the detection area 10, such that preferably only information or signals S or curves K originating from the selected parts or areas are recorded and / or evaluated and / or processed in the further course.

[0427] Selection and / or selective evaluation of information and / or signals S is particularly advantageous since it can save both computing power and thus energy consumption, reducing the computing power that needs to be provided and thus saving resources.

[0428] Step S3 can be carried out together with or simultaneously with step S2 and / or step S1. In particular, measures based on one another can enable, on the one hand, the determination of the presence and / or position of the animal T on the examination apparatus 1 and the presence and / or position of the leg 2 on the sensor device 4, and, on the other hand, the selection of the detector 6 and / or the sensor 7, preferably based on each other or simultaneously or the same signal S. In principle, however, the further steps of the method can also be realised without such a selection and / or separately.

[0429] The selection of the detectors 6 and / or sensors 7 in step S3 is performed in particular automatically, in particular by a search run or scan, and / or on the basis of the determination of the position of the leg 2 performed in step S2. Thus, preferably in step S3, the detectors 6 and / or sensors 7 are selected for which it was determined in step S2 that the leg 2 is located above or covers these detectors 6 and / or sensors 7.

[0430] Step S3 can also be performed repeatedly, in particular if it is found in step S2 or by a new position determination that the position of the leg 2 on the sensor device 4 has changed, for example due to a movement of the leg 2 during the measurement and / or examination and / or recording of the curve K. In this case, preferably one or more other sensors 7 or a different subset of the sensors 7 than before is selected. In particular, this allows the animal T to be examined to move during the examination or the leg 2 to move during the examination. Measurement errors and / or movement artefacts caused by this can be compensated for by selecting the sensor 7 again and / or by a different selection of the sensors 7, in particular in connection with the determination of the position (again) and / or the discarding of unusable curves K or curve sections KA. In particular, during or after the movement of the animal T or the leg 2, it is possible for the examination to be continued or continued with one or more other sensors 7 or a different subset of the sensors 7 than before the movement. The fact that the animal T can preferably move freely during the examination makes the examination very comfortable and stress-free for the animal T. This results in accurate and reliable examinations, in particular blood pressure measurement examinations.

[0431] Furthermore, step S3 or the measures performed in step S3 may advantageously be realized independently of the further steps S4 to S9.

[0432] Step S4 In step S4, one or more measurements are preferably performed, in particular by means of the sensor device 4. In particular, one or more curves K, in particular photoplethysmograms, containing information about the arterial blood flow BF are recorded.

[0433] This can be done using one or more detectors 6 and / or sensors 7. Curve K therefore preferably corresponds to the electromagnetic radiation R detected by detector 6, and in particular to the intensity of this radiation.

[0434] Electromagnetic radiation R preferably originates from an emitter 5. In this connection, the curve K indicates, and preferably contains, information about the arterial blood flow BF, by virtue of the detected electromagnetic radiation R varying with the arterial blood flow BF, in particular its intensity.

[0435] The radiation R emitted by the emitter 5 can be scattered and / or reflected in the leg 2 during examination of the leg 2 and can thus reach the detector 6. This is shown by way of example in Fig. 7. The signal S measured by the detector 6 thus corresponds to the scattering, reflection and / or absorption in the leg 2 of the radiation R emitted by the emitter 5, where the scattering, reflection and / or absorption depends in particular on the volume of blood in the blood vessels extending into the leg 2 and / or on the oxygen saturation of the blood.

[0436] The scattering, reflection and / or absorption measured by the detector 6 and / or the sensor 7, and thus the curve K, is made up of a component that is at least approximately constant in time and a component that varies in time.

[0437] The constancy of the time course of the signal S recorded by the detector 6 or sensor 7 is caused in particular by tissues surrounding the blood vessels, such as muscles, nerves, tendons, bones and / or skin, since scattering and / or absorption by said tissues preferably does not vary or varies only to a small extent. In particular, this at least approximately constant component in time is not correlated with the heartbeat of the animal T. Blood flowing through the veins may also contribute to this at least approximately constant component.

[0438] The time-varying component is preferably caused at least essentially by the arterial blood flow BF, i.e. by the time variations of blood flowing through artery A. Artery A is the blood vessel through which blood is conveyed from the heart. The blood volume or volumetric flow rate through artery A and the oxygen saturation of blood in artery A vary in a manner that correlates with the heartbeat. In particular, the absorption and / or scattering of blood in artery A depends not only on the blood volume or blood flow rate in artery A, but also on the oxygen content or oxygen saturation of blood in artery A.

[0439] In this connection, the time course of a coherently and / or continuously recorded signal S is shown as a curve K. In a graphical representation of the signal S, as shown in Fig. 9, the curve K is the corresponding graph in the figure.

[0440] However, the curve K can also be formed or represented by an equivalent, in particular a data equivalent, of a graph or a course of the signal S. The curve K can also be represented or formed by a number of connected single points or data points, by a vector sequence or the like, even if it is a preferably continuous course. The curve K can be or comprise a digitized analog signal S coming from the detector 6 and / or the sensor 7.

[0441] Particularly preferably, the curve K is a digital signal S in the form of individual data points and / or the curve K is converted into individual data points after acquisition for further evaluation.

[0442] Preferably, the curve K starts at the start of the measurement or recording of the signal S. Preferably, the curve K ends at the end or interruption of the measurement or recording of the signal S.

[0443] A "recording" of a signal S or of a curve K is in particular a preferably temporary or intermediate storage of the signal S or of the curve K. In particular, the term "recording" means a measurement and a simultaneous or intermediate storage of the signal S or of the curve K. The term "recording" therefore also includes a measurement, in particular a photoplethysmography.

[0444] The different curves K can be generated by carrying out different measurements, each of which is recorded, or by recording, storing and / or using (successively) the measured signal S only partially or section by section.

[0445] Preferably, several curves K are recorded simultaneously, in particular by different sensors 7 and / or detectors 6 of the sensor device 4. Alternatively or additionally, several curves K can be recorded in sequence by the same sensor 7 and / or detector 6 and / or several curves K can be recorded in sequence by different sensors 7 and / or detectors 6.

[0446] According to a particularly preferred embodiment, several curves K are thus recorded simultaneously, in particular with different sensors 7, where the different sensors 7 preferably correspond to different regions of the sensor device 4 or leg 2, as explained above, such that resultant curves K from different regions of the sensor device 4 are recorded. Preferably, the curves K are recorded only with the detectors 6 and / or sensors 7 selected in step S3. However, this is not mandatory.

[0447] According to another embodiment, several curves K are recorded in sequence with one detector 6 and / or sensor 7. However, further curves K can be recorded by other sensors 7 simultaneously with the recording of a curve K by this sensor 7 and / or with a time delay.

[0448] In other words, the sensors 7 are preferably separated from one another, even if as described above some of the emitters 5 preferably form part of multiple sensors 7, and multiple curves K can be recorded or are recorded in sequence at each sensor 7, and independently of this, one or more curves K can be recorded or are recorded simultaneously at the other sensors 7.

[0449] However, the sensors 7 are particularly preferably synchronized, so that the curves K are recorded simultaneously with the sensors 7 .

[0450] Particularly preferably, but not necessarily, a heartbeat curve KG, in particular an electrocardiogram and / or an impedance cardiogram, is recorded simultaneously with the curve or curves K. The heartbeat curve KG is recorded in particular by means of electrodes 15. In principle, however, the heartbeat curve KG can also be recorded by means of another detection element, for example a microphone or the like, and thus a phonocardiogram.

[0451] To record the heart rate curve KG, particularly preferably an electrode 15 is used, which is in contact with the leg 2 on which the optical examination by the sensor device 4 takes place. Preferably, a (first) electrode 15A assigned to the sensor device 4 is used for this purpose, which (first) electrode 15A is preferably designed and arranged in such a way that, when the leg 2 is placed on the sensor device, an electrical coupling of the leg 2 with the electrode 15a takes place and at the same time photoplethysmography can be carried out. In the illustrated example, the first electrode 15A is arranged or formed on or in the immediate vicinity of the sensor device 4.

[0452] Preferably, the heart rate curve KG is checked for usefulness, in particular in an automatic or automated manner. The usefulness check can take place during or after the recording of the heart rate curve KG.

[0453] For recording the heart rate curve KG, preferably several electrodes 15 are used, one of which, 15A, may, but need not, be the electrode 15A assigned to the sensor device 4. Furthermore, the testing device 1 comprises one or more electrodes 15, so that the animal T or its different legs 2 or other body parts are preferably electrically coupled or contacted by different electrodes 15.

[0454] Here, one of the electrodes 15, in particular the third electrode 15C, can function as a collector or reference electrode for one or more of the other electrodes 15. Preferably, unipolar and / or bipolar leads are used, in particular following the lead systems of Frank Norman Wilson in 1934, Emanuel Goldberger in 1942 and / or Willem Einthoven in 1913. However, other approaches are also possible here.

[0455] The collection or reference electrode 15C can be used to compensate for DC voltages or set potentials, introduce currents or set potentials in the animal T. The collection or reference electrode 15C preferably serves to measure an average or reference potential that forms a reference point for the potentials measured at the other electrodes 15.

[0456] In principle, one channel of the heart rate curve KG and / or two electrodes 15 are sufficient. The use of at least a third electrode 15 is particularly preferred, which allows for the recording of several heart rate curves KG, in particular ECG channels, which can furthermore be used alternatively to one another or in combination.

[0457] Preferably, the heart rate curve KG is preprocessed, in particular in a preprocessing device 27. In particular, the heart rate curve KG can be filtered, particularly preferably band-pass filtered, whereby low-frequency and high-frequency bands adjacent to the middle frequency band are attenuated. Alternatively or additionally, the heart rate curve KG can be filtered using a notch filter and / or a band-stop filter, whereby certain frequencies or frequency bands are attenuated or suppressed. In particular, disturbances from the power grid, for example disturbances with a frequency of 50 Hz, can be suppressed.

[0458] If the heart rate curve KG is not useful, i.e. does not meet the check criteria for usefulness, the heart rate curve KG is preferably discarded. In particular, if the heart rate curve KG is not useful, the K curves recorded simultaneously with the heart rate curve KG will also be discarded. Preferably, further evaluation is performed exclusively on the curves K and / or the heart rate curve KG that have not been discarded.

[0459] Particularly preferably, if the heart rate curve KG is not available, a new heart rate curve KG and preferably one or more new curves K corresponding to the new heart rate curve KG are recorded, preferably simultaneously with the new heart rate curve KG.

[0460] The usability check is preferably performed on the heart rate curve KG or on a section of the heart rate curve KG which has or corresponds to more than 2, preferably more than 4 and / or less than 20, preferably less than 15, in particular less than 10, most preferably about 6 to 8 heart beats and / or QRS complexes.

[0461] A check of usability is hereby, or alternatively or additionally preferably performed on the heart rate curve KG or on a section of the heart rate curve KG, the length of which is or corresponds to more than 0.5 seconds, preferably more than 1 second and / or less than 10 seconds, in particular less than 5 seconds, particularly preferably less than 3 seconds. Most preferably, the length or section of the heart rate curve KG is approximately 2 seconds, respectively. The length or section of the heart rate curve KG is in particular the duration of the measurement of the heart rate curve KG or section.

[0462] Preferably, one or more criteria are checked when checking the usefulness of the heart rate curve KG. The heart rate curve KG is preferably useful if it fulfills all the criteria described below. In principle, however, other methods are possible in which only some of the criteria described below are checked and / or the heart rate curve KG is also considered useful if only one or a subset of the criteria are fulfilled. Alternatively or additionally, other criteria than those described below may also be provided.

[0463] According to a first criterion, preferably the peak-to-peak amplitude of the heart rate curve KG is determined. A filtered and / or pre-processed heart rate curve KG is preferably used for this purpose. The peak-to-peak amplitude is the difference between the absolute maximum and the absolute minimum of the heart rate curve KG. If the peak-to-peak amplitude is equal to or greater than a specified or specifiable threshold value, the criterion is considered to be fulfilled. Otherwise, the criterion is considered to be not fulfilled.

[0464] According to the second criterion, preferably the power spectrum density or the power distribution of the heart rate curve KG is determined. In particular, it is checked whether the quotient of the integral of the power density spectrum in the first interval and the integral of the power density spectrum in the second interval is greater than or equal to a lower threshold and / or less than or equal to an upper threshold. If the quotient is greater than or equal to a lower threshold and / or less than or equal to an upper threshold, the criterion is considered to be fulfilled. Otherwise, the criterion is considered to be not fulfilled.

[0465] According to the third criterion, preferably the skewness and / or kurtosis of the amplitude distribution function of the heart rate curve KG is examined. If the kurtosis and / or skewness is equal to or greater than a specified or specifiable threshold, the criterion is considered to be fulfilled. Otherwise, the criterion is considered to be not fulfilled.

[0466] According to the fourth and fifth criteria, preferably the Pan-Tompkins plot of the heart rate curve KG is examined.

[0467] The Pan-Tompkins algorithm is an algorithm for detecting the heart rate curve KG, in particular the QRS complex in an electrocardiogram. According to the Pan-Tompkins algorithm, the heart rate curve KG is filtered, derived, squared and then convolved and / or integrated. The curve resulting from these steps or from the application of the Pan-Tompkins algorithm to the heart rate curve KG is called the Pan-Tompkins plot. The QRS complex and / or the R peak of the heart rate curve KG can be reliably determined from the Pan-Tompkins plot.

[0468] It has also been found that in the context of the present invention, the usefulness of the heart rate curve KG can also be checked by means of a Pan-Tompkins plot.

[0469] According to the fourth criterion, the minimum and / or average amplitude of the peaks of the Pan-Tompkins plot are examined. If the minimum and / or average amplitude of the Pan-Tompkins plot is equal to or greater than a specified or specifiable threshold, the criterion is considered fulfilled. Otherwise, the criterion is considered not fulfilled. Different thresholds may be set for the minimum and average amplitudes.

[0470] According to the fifth criterion, the minimum, maximum and / or average distance of the peaks of the Pan-Tompkins plot are examined. If the minimum, maximum and / or average distance of the peaks of the Pan-Tompkins plot is greater than or equal to a lower threshold and / or less than or equal to an upper threshold, the criterion is considered to be met. Otherwise, the criterion is considered not met. Different thresholds may be set for the minimum, maximum and average distances.

[0471] According to the sixth criterion, the degree of saturation of the heart rate curve KG or the signal measured by the electrodes 15 is checked. Saturation of the signal or the heart rate curve KG exists when the signal, when measured by the electrodes 15, assumes a maximum or minimum possible value. Preferably, the sixth criterion is used to determine the proportion, in particular the time proportion, of the signal or the heart rate curve KG measured by the electrodes 15 that is saturated. If that proportion is below a specified or specifiable threshold, the criterion is considered to be fulfilled. Otherwise, the criterion is considered not to be fulfilled. For example, the threshold can be 0.15 or 15%, such that if more than 15% of the heart rate curve KG is saturated, the criterion is not fulfilled.

[0472] Alternatively or in addition to checking the usefulness of the heart rate curve KG, the usefulness of the curve K can be checked. This check of the usefulness of the curve K is preferably carried out after the measurement or recording of the curve K, in particular on the basis of the individual curve sections KA, and preferably if the heart rate curve KG meets the criteria for its usefulness.

[0473] The check of the usability of the curve K is preferably performed in step S6 and is therefore explained in more detail below with respect to step S6. However, it is also possible in principle for the check of the (basic) usability of the curve K to additionally form part of step S4 and / or for the check of usability to be performed during the recording of the curve K. In order to check the usability of the curve K, it is preferably evaluated with respect to criteria, such as for example the expected basic shape, the expected spectrum, the expected amplitude or the like.

[0474] A check of the usefulness of the curve K is carried out after the measurement or recording of the curve K, in particular on the basis of the individual curve sections KA, and preferably if the heart rate curve KG meets the criteria of usefulness.

[0475] In principle, it is not mandatory to check the usefulness of the heart rate curve KG and / or the curve K. However, this has proven to be particularly advantageous for the examination of animals T, in particular domestic dogs or cats, since in a simple and / or fast way useless measurements, i.e. measurements that do not contain any useful information and / or do not result in a reliable evaluation result, can be selected and / or ignored or left not taken into account for further evaluation. In particular, the usability check preferably results in that medical examinations, in particular blood pressure measurements, of the animal T can be carried out even if the animal T is not fixed relative to the examination device 1, in particular relative to the sensor device 4 and / or the electrodes 15, or even if the animal T moves or can move relative to the examination device 1, in particular relative to the sensor device 4 and / or the electrodes 15, during the examination. In particular, the usability check makes it possible to detect and preferably select or not take into account for further evaluation measurements in which the animal T has moved. In this way, the examination can be made particularly comfortable and stress-free for the animal T. This results in reliable and accurate examinations, in particular blood pressure measurements BP.

[0476] Preferably, the duration of the measurement or recording of the curve K is more than 30 seconds and / or less than 60 seconds, in particular about 45 seconds. Here, several curves K and / or heart rate curves KG are preferably recorded simultaneously.

[0477] Particularly preferably, it is determined whether and / or when the animal T, in particular the leg 2, has moved during the recording of the curve K and / or the heart rate curve KG, preferably this is done by checking the position of the leg 2 already described in step S2. Segments of the curve K and / or the heart rate curve KG in which the animal T and / or the leg 2 has moved are preferably removed or cut out from the curve K and / or the heart rate curve KG. Segments in which no movement of the animal T or the leg 2 has occurred or been detected and which have a length of less than 5 seconds or at most 5 seconds are preferably also cut out from the curve K and / or the heart rate curve KG.

[0478] The remaining segments of the curve K and / or the heart rate curve KG, i.e. the segments in which no movement of the animal T or leg 2 was detected and / or the segments that were not removed, are preferably joined together to form in particular a new curve K.

[0479] Preferably, the thus combined curve K or the curve KKG and / or the thus combined heart rate curve KG form the basis for further evaluations or medical tests, in particular for blood pressure measurements. In other words, the further steps S5 to S9 are preferably performed with the curve K and / or the heart rate curve KG from which the segments in which the animal T and / or the leg 2 have moved have been deleted.

[0480] The removal of segments in which the animal T and / or leg 2 have moved is preferably performed in addition to and / or after the (previously explained) usability check of the heart rate curve KG.

[0481] The curve K and / or the heart rate curve KG thus combined has a length of at least 20 seconds, particularly preferably at least 30 seconds, and / or consists only of segments having a length of more than 3 seconds, preferably more than 5 seconds. If these requirements are not met after cutting out the segments in which the movement occurred, the recording of the curve K and / or the heart rate curve KG is preferably restarted or repeated.

[0482] Furthermore, it is also possible that the curve K is composed of segments of multiple curves K measured or recorded with different detectors 6 and / or sensors 7, in particular if the position of the leg 2 is changed during recording of the multiple curves K and / or if the curves K are recorded with different detectors 6 and / or sensors 7 due to such a change in the position of the leg 2.

[0483] During step S4 or during the recording of the curve K and / or the heart rate curve KG, it is particularly preferred that a presence determination, particularly as performed or described in step S1, a position determination, particularly as described in step S2 and / or a position check, particularly as described in step S2, is performed. This is particularly performed automatically, continuously and / or at regular intervals, preferably at intervals of less than 2 seconds or less than 1 second. In particular, it is possible in this way to determine whether the animal T has moved or is moving and / or the position of one or more legs 2 changes. If it is found that the animal T or its legs 2 have moved, the presence and / or position determination is preferably repeated, particularly automatically, and preferably new sensors 7 and / or detectors 6 are selected and, with these newly selected sensors 7 and / or detectors 6, the measurement or recording of the curve K is continued or further or new curves K are recorded, particularly automatically. This is explained below for different situations or phases P1 to P7 that may occur during the examination of the animal T.

[0484] 14 shows, by way of example only, various phases P1-P7 that may occur during the measurement or recording of the heart rate curve KG and / or the curve K. The order of the phases P1-P7 is therefore purely exemplary for purposes of explanation and does not represent a required order of the phases P1-P7. Rather, the phases P1-P7 may occur in any order and the phases P1-P7 may occur multiple times and / or not at all during the examination or recording of the curve K and / or the heart rate curve KG.

[0485] In the following description of phases P1 to P7, it is assumed that the examination apparatus 1 has (at least) two electrodes 15, in particular an electrode 15A for the left (front) leg and an electrode 15B for the right (front) leg of the animal T. It is further assumed that the examination apparatus 1 has only one or exactly one sensor device 4, which is assigned to or positioned under the left (front) leg of the animal T under examination. Preferably, the presence of the animal T is determined by the electrodes 15A, 15B, and the position of the leg 2, in particular the left front leg, is determined and checked with the sensor device 4 and the curve K is recorded. Of course, other versions of the examination apparatus 1 are also possible, in which case the following description applies accordingly.

[0486] Figure 14 shows in four rows R1 to R4 the different actions or results of actions carried out during phases P1 to P7. The horizontal or X-axis of the diagram in Figure 14 represents in particular a time axis.

[0487] In row R1, the result of the presence test carried out in particular in step S1 is shown. During the presence test, it is preferably determined whether the leg 2 of the animal T, in particular the right front leg, is placed on the assigned electrodes 15A, 15B so as to be able to record the heart rate curve KG, as described. Here, the value "1" means that the presence test was successful or that the right front leg is correctly placed (positive result). The value "0" means that the presence test could not be carried out or that the right front leg is not correctly placed (negative result).

[0488] In row R2, the execution of a determination of the position of the leg 2, in particular the left front leg, is shown. The determination of the position is preferably performed by performing a search run or scan with the sensor 7 and / or by determining the center of mass or centroid of the measurement signal S, as described above, in particular in step S2. Here, the value "1" means that a position determination and / or a search run or scan is performed. The value "0" means that no position determination or search run or scan is performed.

[0489] In row R3, the result of a check of the position of leg 2, in particular the left front leg, is shown, which is preferably performed as explained in step S2 above. In particular, as explained, it is continuously and / or periodically checked whether the position of the left front leg has changed compared to an initial or previously determined position. A value of "1" means that the position has been successfully detected or has not changed from the initial or previously determined position (positive result). A value of "0" means that the position has not been detected or has changed compared to the initial previously detected position (negative result).

[0490] In row R4, the performance of measurements or tests is shown, in particular the recording of curve K and heart rate curve KG. The recording of curve K is performed in particular by means of a sensor device 4 on the left front leg of animal T. The recording of heart rate curve KG is performed by means of electrodes 15A, 15B, one electrode 15A contacting the left front leg of animal T and the other electrode 15B contacting the right front leg. A value "1" means that curve K and heart rate curve KG are recorded. A value "0" means that curve K and / or heart rate curve KG are not recorded.

[0491] Phase P1 is in particular a start phase. In phase P1, the animal T is placed on the examination device 1 for examination. In phase P1, a presence determination of the animal T or of the leg 2 is preferably performed first. Once the presence of the animal T has been successfully determined or detected (R1 jumps from 0 to 1), a search run and / or a position determination is preferably performed with the sensor 7 to determine the position of the left front leg (R2 jumps from 0 to 1). Once the position of the left front leg has been successfully determined and thus the search run and / or position determination is terminated (R2 jumps from 1 to 0 and R3 jumps from 0 to 1), a measurement is started and / or at least one curve K and a heart rate curve KG are recorded (R4 jumps from 0 to 1).

[0492] In phase P2, the position of the left front leg changes without removing or lifting it from the sensor device. During this time, the right front leg remains in contact with the assigned electrode 15B. The result of the presence detection during the entire phase P2 is that the leg 2 of the animal is present (R1 has a value of 1). During the position check, the position of the left front leg is determined to have changed compared to the originally determined position (R3 has a value of 1 to 0). The recording of the curve K and the heart rate curve KG is therefore interrupted or terminated (R4 has a value of 1 to 0) and a new position determination is made (R2 has a value of 0 to 1). Once the (new) position of the left front leg has been successfully determined (R2 has a value of 1 to 0 and R3 has a value of 0 to 1), a new recording of the curve K and the heart rate curve KG is started or the recording of the curve K and the heart rate curve KG is continued (R4 has a value of 0 to 1).

[0493] In phase P3, first the right front leg is lifted from the assigned electrode 15B and then placed on the electrode 15B again. During this time, the position of the left front leg does not change. Therefore, when or after the right front leg is lifted, the result of the presence detection becomes negative (the value of R1KG jumps from 1 to 0). Since the position of the left front leg does not change, the result of the position check becomes positive and no new position determination is performed (the value of R3 remains constant 1 and the value of R2 remains constant 0). Since the right front leg is lifted from the electrode 15B, the heart rate curve KG is not recorded and the recording of the curve K and the heart rate curve KG is interrupted or terminated (the value of R4 jumps from 1 to 0). After the right front leg is returned to the electrode 15B, the result of the presence detection becomes positive again (the value of R1 jumps from 0 to 1). Therefore, the recording of the curve K and the heart rate curve KG continues (the value of R4 jumps from 0 to 1).

[0494] In phase P4, the left front leg is lifted from the sensor device 4 and the assigned electrode 15A and then placed again in the same position on the sensor device 4 and the assigned electrode 15A. When or after the lifting of the left front leg, the result of the presence detection is negative (the value of R1 jumps from 1 to 0). Also the result of the position check is negative (the value of R3 goes from 1 to 0). The recording of the curve K and the heart rate curve KG is therefore interrupted or stopped (the value of R4 goes from 1 to 0). When the left front leg is placed again on the assigned electrode 15A and the sensor device 4 (in the same position as before), the result of the presence detection is again positive (the value of R1 jumps from 0 to 1) and also the result of the position check is positive (the value of R3 jumps from 0 to 3). As the position of the left front leg has not changed compared to the previously determined or previously stored position, no new position determination is performed (the value of R2 remains constant 0). After the left foreleg 2 is placed again, a new recording of the curve K and the heart rate curve KG begins or the recording of the curve K and the heart rate curve KG is continued (the value of R4 jumps from 0 to 1).

[0495] In phase P5, the left front leg is lifted from the electrode 15A and / or the sensor device and then placed again in a changed position on the sensor device 4 and the assigned electrode 15A. After lifting the left front leg, the presence detection and position check result becomes negative (R1 and R3 jump from 1 to 0) and the recording of the curve K and the heart rate curve KG becomes interrupted or terminated (R4 jumps from 1 to 0). As soon as the leg is put back, the presence detection result becomes positive (R1 jumps from 0 to 1). As the position has changed, the position detection result remains initially negative (R3 remains 0) and the position of the left front leg is determined again (R2 jumps from 0 to 1). When a new position for the left front leg is successfully determined and the position determination is completed (the value of R2 jumps from 1 to 0 and the value of R3 jumps from 0 to 1), a new recording of curve K and heart rate curve KG is started or recording of curve K and heart rate curve KG is continued (the value of R4 jumps from 0 to 1).

[0496] In phase P6, the animal T or both front legs are moved away from the assigned electrodes 15A, 15B. The result of the presence detection and location check is therefore negative (the values ​​of R1 and R3 jump from 1 to 0) and the recording of the curve K and the heart rate curve KG is interrupted or terminated (the value of R4 jumps from 1 to 0). The value of R2 is always 0, since no re-presence of the animal T is detected.

[0497] In phase P7, the front legs contact the assigned electrodes 15A, 15B, but the left front leg is positioned in such a way that a position cannot be determined and / or a meaningful measurement cannot be made. The result of the presence detection is therefore negative (the value of R1 jumps from 0 to 1). A repeated position determination is performed without good results (the value of R2 alternates between 0 and 1, the value of R3 is 0). Thus, neither the curve K nor the heart rate curve KG is recorded (the value of R4 is 0).

[0498] Step S4 or the recording and / or checking of the usefulness of one or more heart rate curves KG and / or curves K can also be performed several times or several times in succession, in particular even after an evaluation or partial evaluation of the curve K has already been performed, in particular according to one of steps S5, S6, S7, S8 and / or S9. For example, the evaluation may reveal that there are not enough useful curve sections KA and therefore further curves K have to be included. This can be caused, for example, by a movement of the animal T or of the leg 2.

[0499] In particular, the multiple recording of the heart rate curve KG and / or the curve K or the repetition of step S4 allows the animal T to move during the examination and / or to move the leg 2 during the examination. Measurement errors and / or movement artefacts resulting from this can be compensated for by multiple recording of the heart rate curve KG and / or the curve K, in particular in connection with multiple presence detections and / or selection of sensors 7 and / or discarding of unusable curves K or curve sections KA. In particular, during or after the movement of the animal T or the leg 2, it is possible to continue or continue the examination with one or more other sensors 7 or a different subset of sensors 7 than before the movement. The fact that the animal T can preferably move freely during the examination makes the examination very comfortable and stress-free for the animal T. This results in accurate and reliable examinations, in particular blood pressure measurement examinations.

[0500] Step S5 In step S5, the curve K is preferably cut into curve sections KA in such a way that each curve section KA corresponds to one heart beat, and particularly preferably each curve section KA corresponds exactly to one heart beat.

[0501] Carving or slicing the curve K in the sense of the present invention is preferably understood as a division or partitioning of the curve K along the time axis. In this way, the curve K is divided into temporal sections. This can be realized by data processing in such a way that the beginning and / or end of the curve sections KA are identified and / or marked. In principle, it is possible to separate the curve sections KA from one another. In further processing, the curve sections KA are also preferably treated separately. However, in this context, "slicing" or "carving" does not necessarily mean a physical separation of the resulting curve sections KA from one another.

[0502] As can be seen from the example curve K shown in figure 9, which corresponds to a photoplethysmogram actually measured in a cat and which is usually in contrast to the heart rate curve KG in particular, the regularity or periodicity of the curve K, in particular its correlation with the heart rate, cannot be directly ascertained. It is therefore advantageous to use information from the heart rate curve KG to section the curve K and then perform a further evaluation on the basis of the individual curve sections KA.

[0503] In the following, the cutting or slicing of a curve K will be explained by taking a single curve K as an example. Preferably, all recorded curves K are cut into curve sections KA in the same way.

[0504] The cutting of the curve K into curve sections KA is preferably automated or performed in an automated manner.

[0505] Particularly preferably, the curve K is divided into curve sections KA using information of the heart rate curve KG recorded simultaneously with the curve K. In principle, however, other methods are also conceivable.

[0506] The use of the heart rate curve KG to slice / divide the curve K into curve sections KA is particularly advantageous since the time TH of the heart beat can be determined particularly easily and reliably in the heart rate curve KG and the curve K can be divided at or based on this time TH.

[0507] Preferably, the times TH of the heart beats are determined on the basis of the heart beat curves KG, and the curves K at these times TH are cut into curve sections KA. Preferably, each curve section KA starts at the time TH of one heart beat and ends at the time TH of the immediately following heart beat.

[0508] However, in general, an exact determination of the end of the curve section KA is not important, since the curve section KA serves in particular for an accurate or reliable determination of the curve feature M. For this purpose, it is of paramount importance to select as accurately as possible the time TH of the heartbeat as the beginning of the curve section KA and / or to select as accurately as possible the same point relative to the time TH of the heartbeat as the beginning of the curve section KA.

[0509] Preferably, the curve sections KA are of equal length and / or the curve K is cut into curve sections KA each having the same length. Preferably, the length of the curve section KA corresponds to the average heart rate or corresponds to the duration between the times TH of two (closest) successive heart beats at this heart rate or corresponds to this. This simplifies the determination of the usefulness or quality of the curve K or the curve section KA and has been shown to allow the measurement of the blood pressure BP to be performed with greater accuracy.

[0510] The average heart rate is preferably in particular the arithmetic mean and / or median value of the heart rate, in particular the heart rate being determined by the heart rate curve KG. By "heart rate" is meant in particular the (average) number of heart beats per unit of time, in particular per minute. For example, if the average heart rate is 120 bpm, this corresponds to a (average) duration of a heart beat of 0.5 seconds or a (average) interval between two heart beats of 0.5 seconds.

[0511] The length L of the curved section KA is preferably determined by the formula: L=d HB Determined by a, where d HB is the average duration of a heart beat, determined in particular on the basis of the average heart rate, and a is a factor having a value preferably equal to or greater than 1. By means of the factor a, the length L of the curve section KA can also be selected to be greater than the average duration of a heart beat. This has proven to be advantageous for determining the usefulness or quality of the curve K or the curve section KA and for measuring the blood pressure BP.

[0512] Thus, the length of the curve section KA can be selected independently of the specific / respective duration between the time TH of two successive heart beats.

[0513] As described, the curve sections KA preferably each begin at a time TH of a heart beat and are equal in length, allowing the curve sections KA to overlap and / or for a segment of the curve K to be included in multiple curve sections KA, particularly when the length of the curve sections KA is greater than the distance between two adjacent heart beats.

[0514] Particularly preferably, the heart rate curve KG is an electrocardiogram. In particular, on the basis of the electrocardiogram, various characteristic structures can be identified which can be assigned to or result from different phases of the heart's activity. In the present method, the so-called QRS complex is of particular importance.

[0515] In figure 9 the different QRS complexes of the heart rate curve KG are marked, one QRS complex preferably representing one heart beat.

[0516] Preferably, the location of one or more QRS complexes of the heartbeat curve KG are used to cut the curve K into curve sections KA. In particular, the QRS complexes of the heartbeat curve KG are used to determine the time TH of the heartbeat, and preferably the curve K is cut into curve sections KA at the time TH determined by the QRS complex. In other words, the QRS complexes or parts thereof are information on the means by which the curve K is cut into sections KA.

[0517] The QRS complex preferably has three peaks, in particular a Q peak, an R peak and an S peak.

[0518] As the Q peak, the initial, specifically negative or downward deflection or peak of the QRS complex is designated.

[0519] The R peak refers specifically to the negative or downward deflection or peak of the QRS complex that follows the Q peak.

[0520] The S peak refers specifically to the positive or upward deflection or peak of the QRS complex following the R peak.

[0521] In particular, the position of the R-peak or the position of the maximum of the R-peak can be used as the time TH of the heart beat, which is shown as an example in FIG.

[0522] Also, instead of using the R peak as the time TH of the heartbeat, it is conceivable to use other structures or other characteristic points of the heartbeat curve KG, such as the Q peak, the S peak, a midpoint or an inflection point between two peaks, in particular the R peak and the S peak, or the like.

[0523] The determination of the R-peak or its position is preferably made by means of a Pan-Tompkins plot of the heart rate curve KG, as will be explained in more detail below.

[0524] For the determination of the R peak, preferably first all local peaks, in particular all maxima of the Pan-Tompkins plot, are determined.

[0525] As explained above, the heart rate curve KG, and therefore also the Pan-Tompkins plot, preferably exists as a set of discrete data points di, where d is the value of the Pan-Tompkins plot at location i. The subscript i counts through the data points di and preferably corresponds to the time at which each data point di was measured. In particular, a local maximum of the Pan-Tompkins plot is thus represented by a data point di and / or a portion of the data points di represents a local maximum of the Pan-Tompkins plot.

[0526] Data point d i is especially d i >d (i-1) and d i >d (i+1) applies, i.e., data point d i A local maximum is represented when the value of is greater than the values ​​of the adjacent data points.

[0527] Data point d showing the maximum i Then, in the next step, preferably, the data point d i Only those data points with higher values ​​are selected within a certain interval around the interval, which preferably has a width of more than 200 ms, in particular more than 300 ms, and / or less than 600 ms, preferably less than 500 ms, in particular less than 400 ms. Particularly preferably, the interval has a width between 300 ms and 400 ms, for example about 372 ms.

[0528] The peak or data point of the Pan-Tompkins plot thus determined or selected, i For , preferably the embrasure height or prominence is determined.

[0529] Preferably, the peak or data point d is defined as the R peak of the Pan-Tompkins plot whose autonomous height or prominence is equal to or exceeds a specified or identifiable threshold. i Only the above is selected or determined.

[0530] The threshold is preferably an adaptive threshold. An adaptive threshold in the sense of the present invention preferably varies with every data point d i For different thresholds or different data points d i For example, individual thresholds ti are set for each time point i or each data point d i Preferably, an adaptive threshold t i is determined, in particular, for each point i by determining and / or calculating the convolution between the Pan-Tompkins plot and a window function. Then, the threshold t i Specifically, is the value of the convolution of the Pan-Tompkins plot with the window function at position i.

[0531] In principle any window function can be used. Particularly preferably, the window function is the Blackman-Nuttall window. Preferably, a window width of 0.6 seconds and / or a gain factor of 3 is used. However, other values ​​are also possible here.

[0532] Preferably, the position of the R-peak thus determined is also corrected, i.e. the position of the R-peak in the Pan-Tompkins plot may be slightly shifted compared to the position of the R-peak in the original heartbeat curve KG and / or the shift of the peak may be caused by convolution with a window function. Therefore, the position of the R-peak determined by the Pan-Tompkins plot may be "inaccurate" or may differ from the position of the R-peak in the raw signal of the heartbeat curve KG and / or the filtered heartbeat curve KG.

[0533] Correcting the location of the R-peak prevents potential shifts caused by application of filters and / or unintentional use of the Q-peak instead of the R-peak to generate the Pan-Tompkins plot. Correcting the location of the R-peak therefore allows for accurate determination of the heart rate, resulting in reliable or accurate testing of the animal's T, particularly blood pressure measurements.

[0534] The correction of the R-peak position is preferably performed based on a filtered and / or preprocessed heart rate curve KG, but can also be based on the unprocessed heart rate curve KG, in other words the "raw signal" of the heart rate curve KG.

[0535] Preferably, for the correction of the position of the R-peak, starting from the position determined by the Pan-Tompkins plot, this position of the R-peak is preferably searched for or determined in the heart rate curve KG, in particular in the filtered and / or preprocessed heart rate curve KG. This position in the heart rate curve KG, in particular in the filtered and / or preprocessed heart rate curve KG, is then preferably used as the position of the R-peak, in particular replacing the position of the R-peak determined by the Pan-Tompkins plot.

[0536] Particularly preferably, the gradient or slope or derivative of the heart rate curve KG at the position of the R-peak determined by the Pan-Tompkins plot is determined on the heart rate curve KG, and on the basis of this, the next maximum of the heart rate curve KG is searched for and / or determined. Preferably, if the gradient or slope or derivative is positive, it is preferred to go to the right on the heart rate curve KG and / or to examine the next data point on the heart rate curve KG. If the gradient or slope or derivative is negative, it is preferred to go to the left on the heart rate curve KG and / or to examine the previous data point. At this point, in particular at the next or previous data point, the gradient or slope or derivative of the heart rate curve KG is preferably determined again, in particular compared with the previous value of the gradient or slope or derivative. These steps are preferably repeated until a position is found where the gradient or slope or derivative has a minimum value or a minimum amount. This position is the position of the R-peak.

[0537] In simpler terms, based on the slope, the heart rate curve KG is sampled or scanned in the direction of the maximum value until the slope or its absolute value reaches a value of zero and / or a minimum value and thus the maximum value of the heart rate curve KG is obtained.

[0538] This method for determining the position of the maximum and / or R peak in the heart rate curve KG has the advantage that the positions can be calculated quickly, the corresponding algorithms are simple to implement and at the same time the positions are determined reliably.

[0539] However, other methods or algorithms for determining and / or correcting the position of the maximum and / or R-peak in the heart rate curve KG are also conceivable.

[0540] For example, the maximum value of the heart rate curve KG can be determined in the section around the location of the R peak determined by the Pan-Tompkins plot.

[0541] Alternatively or additionally, the three highest peaks can be determined in an interval around the position of the R peak determined by the Pan-Tompkins plot, and it is possible to check whether the first and third of these peaks point in a different direction than the second or central peak, i.e. whether the first and third peaks represent a maximum value and the second peak a minimum value, or vice versa (the first and third peaks represent a minimum value and the second peak a maximum value). If yes, the second or central peak represents the R peak, and therefore its position is determined as the search or correction position of the R peak.

[0542] In general, various methods of determining the maximum or R-peak of the cardiogram KG are conceivable in order to correct the position of the R-peak determined by the Pan-Tompkins plot.

[0543] The determination of the R-peak of the heart rate curve KG is preferably performed after step S4, but alternatively or additionally, the determination of the R-peak can also be performed before and / or during step S4, in particular the usability check of the heart rate curve KG.

[0544] Preferably, saturated sections of the heart rate curve KG are removed, in particular for the purpose of measuring the blood pressure BP and / or the pulse transit time PTT. A section is particularly saturated if the signal within the section assumes the maximum or minimum theoretically possible signal value. Saturated signals can occur, for example, if the leg 2 is moved and / or removed during the measurement.

[0545] Preferably, a saturated section of the heart rate curve KG is deleted if it reaches or exceeds a certain minimum length, preferably more than 10 ms and / or less than 20 ms, for example 12 ms or 15 ms.

[0546] Furthermore, preferably, R-peaks that are below a minimum distance in time from the saturated section, for example less than 200 ms or 100 ms before or after the saturated section (already determined), are removed from the cardiogram KG.

[0547] If a saturated section is deleted from the heart rate curve KG, then preferably the section of the curve K which corresponds to the saturated section of the heart rate curve KG is also removed, whereby a corresponding section in this sense means in particular a section of the curve K which was recorded or measured simultaneously with the saturated section of the heart rate curve KG.

[0548] Preferably, R-peaks that are below a (previously determined) minimum distance in time from adjacent R-peaks are removed from the heart rate curve KG, where preferably both R-peaks that are below the minimum distance are deleted from the heart rate curve KG.

[0549] The minimum distance is preferably determined or defined based on the degree of dispersion of the distribution of the R-peaks of the heart rate curve KG, for example based on the interquartile range or the standard deviation. In particular, the minimum distance is determined in such a way that R-peaks that are far below the average distance of the R-peaks are eliminated.

[0550] For example, the minimum distance is defined or determined by the formula: MA=Q1-f·IQR, where MA is the minimum distance, Q1 is the value of the lower quartile (0.25 quartile), IQR is the interquartile range, i.e., the difference between the upper quartile (0.75 quartile) and the lower quartile, and f is a factor preferably having a value greater than or equal to 1, for example 1.5.

[0551] If an R-peak or a section with an R-peak is deleted from the heart rate curve KG, then preferably the corresponding section of the curve K is also deleted. A corresponding section in this sense is understood in particular to be a section of the curve K which was recorded or measured at the same time as the section of the heart rate curve KG which is deleted from the heart rate curve KG.

[0552] Step S5 may be performed multiple times and / or repeatedly, especially if one or more of the previous steps S1, S2, S3 and / or S4 are performed multiple times and / or repeatedly, thereby resulting in accurate and reliable testing, especially blood pressure measurements, especially if the animal T or leg 2 moves during the test.

[0553] Step S6 The curve K is preferably filtered. This is preferably already performed at least partially in a preprocessing device 30 assigned to the detector 6 and / or the sensor 7. Alternatively or additionally, filtering can also take place before or after the formation of the curve section KA. By means of filtering, disturbing influences in frequency ranges not resulting from influences caused by the pulse wave are removed in an advantageous manner, whereby parts of the curve K or the curve section KA containing information on the arterial blood flow BF are removed. Filtering can take place in connection with this step S6 or beforehand, but this is not essential.

[0554] Prior to further evaluation, in particular the determination of the curve characteristics M according to the curve sections KA, preferably some curve sections KA or a subset of the curve sections KA are selected, and the curve sections KA not specifically selected are discarded.

[0555] Usually, it is not possible to directly tell from the course of the curve section KA whether it is useful or not. This is especially evident from the curve shown in Figure 9, which at first glance appears to be chaotic and does not contain any useful information. It should be emphasized here that the curve K depicted in Figure 9 is not a randomly selected curve K, but corresponds to a photoplethysmogram actually measured in a cat.

[0556] However, in the context of the present invention, it has surprisingly been found that a reliable determination of the curve feature M can nevertheless preferably be achieved by means of the proposed means, in combination. In particular, by the selection and / or exclusion of the curve section KA, movement artifacts can be compensated, so that the examination can be carried out, in particular during an examination using a sensor device, even if the animal T or the leg 2 moves particularly with respect to the sensor device, the blood pressure BP can be reliably measured.

[0557] Particularly preferably, the selection of the curve section KA is carried out based on specific criteria which will be described in more detail below. In particular, the usefulness of the curve K or the curve section KA can be evaluated, and the evaluation result can be improved by discarding the unusable curve section KA.

[0558] In particular, a more accurate determination of the curve feature M can be achieved if the unusable curve section KA is selected, or discarded, or no longer considered.

[0559] The curve section KA is preferably checked for usefulness, in particular by means of check criteria. Preferably, a useful curve section KA is selected and / or an unusable curve section KA is discarded. The discarded curve section KA is not used for further evaluation.

[0560] Preferably, a subset of the (usable) curve section KA is selected for further evaluation and a subset of the (unusable) curve section KA is discarded.

[0561] In particular, the check of the usefulness of the curve section KA constitutes a check of the usefulness of the curve K from which the curve section KA was generated. Thus, the exclusion of an individual curve section KA of the curve K or the exclusion of a subset of the curve sections KA of the curve K in particular constitutes a partial exclusion of the curve K. Similarly, the exclusion of all curve sections KA of the curve K constitutes the exclusion of the (complete) curve K.

[0562] Alternatively or additionally, potentially suitable curve sections KA are selected or chosen based on a check of the usefulness of the curve sections KA. The selected or chosen curve sections KA are used for further evaluation. However, the non-selected or unchosen curve sections KA are not used as a basis for further evaluation, i.e. they are discarded.

[0563] The curve sections KA, which are checked for usefulness and selected or discarded, can originate from different curves K. In this case, the curve sections KA can originate from different curves K, which have been recorded in succession with the same sensor 7 and / or detector 6.

[0564] Alternatively or additionally, the curve section KA can originate from a curve K recorded simultaneously or successively with different sensors 7 and / or detectors 6 .

[0565] Preferably, when checking the usefulness of a curve section KA, one or more criteria are checked: A curve section KA is preferably useful if one, several or all of the criteria described below are fulfilled.

[0566] According to the first criterion, preferably the amplitude of the first extremum of the curve section KA is determined, in particular the amplitude of the absolute maximum. If the amplitude of the first extremum or its absolute value is equal to or greater than a specified or specifiable threshold, the criterion is preferably considered to be fulfilled. Otherwise, the criterion is preferably considered to be not fulfilled.

[0567] Alternatively or in addition to the amplitude of the first extremum, according to a first criterion the peak-to-peak amplitude of the curve section KA can be determined and preferably compared with a specified or prescribable threshold. The peak-to-peak amplitude is the difference between the absolute maximum and the absolute minimum of the curve section KA. If the peak-to-peak amplitude or its absolute value is greater than or equal to the specified or prescribable threshold, the criterion is preferably considered to be fulfilled. Otherwise, the criterion is preferably considered to be not fulfilled.

[0568] The first criterion allows for the discarding of curve sections KA with a particularly flat course, since it has been found that such curve sections KA do not contain any useful information, in particular maxima and therefore an accurate or reliable determination of the pulse transit time PTT and / or other curve features M is particularly difficult, and therefore the accuracy and / or reliability of the evaluation is increased if such curve sections KA are discarded.

[0569] According to the second criterion, it is preferably checked whether a valid value of the curve characteristic M, in particular the pulse transit time PTT, results or can result from the curve section KA. In particular, for this purpose, the position of a first, preferably absolute maximum, of the curve section KA is determined, which preferably corresponds to the pulse transit time PTT. If this position is equal to or greater than a lower specified or specifiable threshold and / or equal to or less than an upper specified or specifiable threshold, the criterion is considered to be fulfilled. Otherwise, the criterion is considered to be not fulfilled.

[0570] Here, the lower threshold value preferably corresponds to a minimum pulse transit time PTT and / or the upper threshold value corresponds to a maximum pulse transit time PTT.

[0571] In this way, curve sections KA that result in biologically, physically or anatomically unrealistic pulse transit times PTT, in particular too low and / or too high, can be eliminated. Due to biological, physical or anatomical principles, the pulse transit time PTT can only exist within a certain interval. For example, there is a certain minimum time between a heartbeat and the arrival of a pulse wave caused by the heartbeat at a certain location in the artery A. Thus, a very small pulse transit time PTT below a lower threshold is not realistic. On the other hand, an upper threshold can also be used, which corresponds to a pulse transit time PTT that is not realistic to reach or exceed.

[0572] For example, for a domestic cat testing on the (front) leg 2, the lower threshold may be defined as 20 ms and the upper threshold as 175 ms. However, for other animal species or body parts, other thresholds and / or minimum and / or maximum pulse transit times PTT may be appropriate or specifiable.

[0573] According to the third criterion, the course of the curve K in the curve section KA is preferably examined or checked. For this purpose, the curve K is in particular smoothed and preferably the first derivative of the smoothed curve K as well as the zeros of the first derivative are calculated. The criterion is considered to be fulfilled if the number of zeros of the first derivative of the preferably smoothed curve K is at least 2 and / or at most 4 and the slope of the first derivative of the curve K or the slope of the second derivative of the curve K at the first position of the first zero of the first derivative is negative. Otherwise, the criterion is considered not to be fulfilled.

[0574] The third criterion checks in particular whether the curve K has a wavy course with essentially different maxima and different minima, with the maxima first and then the minima being assumed. Such an "optimal" course is shown as an example on the right side of Figure 12.

[0575] The first, second and third criteria are preferably absolute criteria, i.e. criteria in which the curve section KA is considered or analysed or checked for usefulness alone, in particular without taking into account other curve sections KA in this check.

[0576] The further criteria described below are preferably relative criteria, i.e. criteria in which the usefulness of a curve section KA is checked by taking other curve sections KA into account and / or by comparison with results determined on the basis of other curve sections KA, such as other curve sections KA or average values.

[0577] The fourth, fifth and sixth criteria preferably check whether a particular curve section KA deviates too much from other curve sections KA, in particular the fourth to sixth criteria serve to filter out or discard extreme outliers.

[0578] The fourth, fifth and / or sixth criterion is preferably checked separately for each curve K and / or for each sensor 7 and / or detector 6. In particular, when checking the curve sections KA of the fourth, fifth and / or sixth criterion, only the curve sections KA that are assigned to the same curve K and / or the same sensor 7 and / or detector 6 are taken into account or used.

[0579] In the fourth, fifth and / or sixth criterion, the curve sections KA are preferably scaled, in particular normalized, so that the curve sections KA, in particular the curve sections KA selected in step S5, have the same amplitude, average value, maximum and minimum values ​​and / or peak-valley values, which makes it easier to compare the curve sections KA.

[0580] It is then preferred to determine a curve mean value KM from the curve section KA, i.e. the mean value of the course of the curve section KA. The curve mean value KM is in particular the mean or mean course of the curve section KA or the curve K in the curve section KA. In particular, the curve mean value KM is determined by calculating the mean value at each point in time of the curve section KA or the mean value at this point in time. This mean value is preferably the arithmetic mean value or the median value, but can also be another mean value.

[0581] By way of example, the averaging of the curve sections KA or the determination of the curve mean value KM preferably corresponds to a superposition of the curve sections KA and a subsequent determination of the average course of the superposed curve sections KA.

[0582] Averaging in this sense based on multiple curve sections KA is shown as an example graphically in FIG. 12, where on the left side of FIG. 12 different curve sections KA are shown, in the center of FIG. 12 the curve sections KA are superimposed and on the right side of FIG. 12 the curve average value KM determined from the curve sections KA is shown.

[0583] Viewed another way, the curve mean value KM is the sum or superposition of the curves K or curve sections KA.

[0584] Each curve section KA preferably corresponds to a separate data point (t i (KAj) , k i (KAj) ) in the form of the j-th curve section KA. i (KAj) , k i (KAj) ), where i is an index that counts the data points.

[0585] Here, t i (KAj) Specifically, the x-coordinate of the i-th data point (t i (KAj) , k i (KAj)In the following, the x-coordinate or physical quantity t i (KAj) is called the position of the i-th data point. i (KA j ) is preferably a data point (t i (KAj) , k i (KAj) ) and in particular the data point (t i (KAj) , k i (KAj) ) corresponds to a (temporal) distance of

[0586] Furthermore, k i (KAj) is the y-coordinate of the i-th data point, i.e., the position t i (KAj) In the following, the y-coordinate or physical quantity k i (KAj) is referred to as the value of the i-th data point.

[0587] The formation of the curve mean value KM involves the determination of the mean value of the curve at a certain position or at a certain time t i (KAj) The value k in i (KA j ) are summed. The result is preferably normalized. The curve mean value KM is therefore preferably calculated as i (KM) , k i (KM) ), especially k i (KM) is the position or time t i (KM) The value of the curve section KA at k i (K) Preferably, therefore,

number

[0588] Physical quantity t of the data points of the curve section KA i (KAj) , k i (KAj) Similarly, the physical quantity t i (KM) is called the location of the i-th data point of the curve mean value KM, and the physical quantity k i (KM) is called the value of the i-th data point of the curve mean KM.

[0589] After the curve mean value KM is determined, a correlation coefficient, in particular an empirically determined correlation coefficient (also called product moment correlation coefficient), in particular a Pearson correlation coefficient or a Pearson product moment correlation coefficient, of the curve section KA to be checked for its usefulness relative to the average curve section is calculated for the curve section KA to be checked. If the correlation coefficient reaches or exceeds a specified or specifiable threshold, the criterion is considered to be met. Otherwise, the criterion is considered to be not met. For example, the threshold can be 0.5.

[0590] The correlation coefficient is preferably calculated using the following formula:

number

number

number

[0591] where r j is the correlation coefficient of the jth curve section KA,

number

number

[0592] In the fourth criterion, preferably, the deviation of the distance between two extrema of the curve section KA is checked in comparison with the distance between the extrema of the remaining curve sections KA. The distance between two extrema or the peak-to-peak distance is understood here in particular as the time distance or the distance of the positions of the absolute extrema, in particular thus the distance of the extrema on the x-axis. As can be seen, for example, from FIG. 12, the curve sections KA preferably each have two absolute extrema, in particular an absolute maximum and an absolute minimum. The distance between the extrema is in particular the difference between the position PM2 of the minimum and the position PM1 of the maximum, or the absolute value of this difference.

[0593] In particular, the fourth criterion involves the determination, for each curve section KA, of the extreme values ​​(peak-to-peak distance), the lower quartile (0.25-quartile), the upper quartile (0.75-quartile) and the interquartile range, i.e. the difference between the upper and lower quartile, the peak-to-peak distance or the distribution of the peak-to-peak distances. The criterion is preferably considered fulfilled if the peak-to-peak distance of the examined curve section KA reaches or exceeds an upper specified or specifiable threshold and / or reaches or falls below a lower specified or specifiable threshold. The upper threshold is preferably the sum of the upper quartile or its position and the product of the coefficient f and the interquartile range, i.e.: UTV=Q3+f IQR, where UTV is the upper threshold, Q3 is the upper quartile or its location, and IQR is the interquartile range. The lower threshold is preferably the difference between the lower quartile or its location and the product of a factor f and the interquartile range, i.e.: LTV=Q1-f·IQR, where LTV is the lower threshold, Q1 is the lower quartile or its location, and IQR is the interquartile range. The coefficient f is preferably greater than 1 and particularly preferably has the value 1.5.

[0594] According to a fourth criterion, in particular curve sections KA that have a particularly large and / or particularly small peak-to-peak distance (compared to the other curve sections KA) can be selected or discarded.

[0595] The fifth criterion is preferably the variance of the value of the curve section KA k compared to the variance of the values ​​of the other curve sections KA. i (KAj) The deviation of the variance or sample variance is examined.

[0596] In particular, in the fifth criterion, the value k i (KAj) The variance or sample variance, the lower quartile value (0.25-quartile), the upper quartile value (0.75-quartile), the interquartile range, i.e. the difference between the upper and lower quartiles, or the distribution of variances, is calculated for each curve section KA. The variance of the values ​​of the j-th curve section KA is preferably calculated by the following formula:

number

number

[0597] The fifth criterion is preferably considered to be met if the variance of the values ​​of the examined curve section KA reaches or exceeds an upper specified or specifiable threshold and / or reaches or falls below a lower specified or specifiable threshold. The upper threshold is preferably the sum of the upper quartile value or its position and the product of the factor f and the interquartile range. The lower threshold is preferably the difference between the lower quartile value or its position and the product of the factor f and the interquartile range. The factor f is preferably greater than 1 and particularly preferably has a value of 1.5.

[0598] According to a fifth criterion, in particular curve sections KA can be selected or excluded whose values ​​show a particularly large and / or a particularly small variance.

[0599] In the sixth criterion, preferably, the difference between the curve section KA and the curve mean value KM is calculated, i.e. in particular for each position t i (KAj) For the difference k i (KAj) -k i (KM) Then, for the resulting curve or difference curve, the spectral power density is calculated for a specified or specifiable frequency range, for example 15 Hz to 40 Hz. If the integral of the spectral power density in this frequency range is less than or equal to a specified or specifiable threshold, the criterion is considered fulfilled. Otherwise, the criterion is considered not fulfilled.

[0600] By selecting the curve section KA on the basis of the described criteria, it is possible to determine the curve characteristic M, preferably on the basis of a heart beat or curve section KA of a maximum value of 200, preferably of a maximum value of 100, particularly preferably of a maximum value of 60, particularly preferably of a maximum value of 45, particularly preferably of a maximum value of 30. This makes it possible to keep the time required for measuring or recording the curve K and / or the heart beat curve KG as short as possible.

[0601] All or part of the criteria may be applied and alternatively or additionally other criteria may be used to check the usefulness of the curve K or the curve section KA.

[0602] The curve section KA is preferably discarded and / or not used for further evaluation if one of the described criteria is not met. If the curve section KA meets all of the criteria or all applied criteria, the curve section KA is preferably selected or used for further evaluation.

[0603] Preferably, the curve section KA is selected only if it fulfills all of the described criteria. In principle, however, other methods are possible, which check only one or some of the described criteria and / or select the curve section KA even if only one or some of the criteria are fulfilled. Alternatively or additionally, criteria other than those described may be provided.

[0604] Alternatively or additionally, for the assessment or check of the usefulness of the curve section KA, the measurement results with the force sensor 18A and / or the scale 18 can be taken into account. For example, a low measurement value can be an indication that the animal T or the leg 2 is not correctly positioned on the sensor device 4, and accordingly the curve section KA is discarded.

[0605] By checking the usefulness of the curve sections KA and / or selecting useful curve sections KA and / or discarding unusable curve sections KA, it is possible to reduce or minimize the number of curve sections KA required for the evaluation and thus the measurement time. This is advantageous for making the examination as quick and comfortable as possible and therefore stress-free for the animal T. This is particularly advantageous for accurate and reliable examinations, in particular blood pressure measurements. Also, the probability of making meaningful measurements during the movement of the animal T is increased.

[0606] In particular, the number of curve sections KA required is reduced by reducing the scatter or variance of the curve sections KA by discarding unusable curve sections KA, which in turn improves the statistics.

[0607] In particular, a large number of measurements is required to obtain a reliable average value or the like when the scatter or variance of the measurements is large, i.e. when the measurement results differ greatly. The better the agreement of the measurements, the fewer measurements are required for good statistics. Thus, the culling of unusable curve sections KA synergistically leads to fewer curve sections KA being required for evaluation in the first place.

[0608] In particular, step S6 can be performed multiple times and / or repeatedly, especially if one or more of the preceding steps S1, S2, S3, S4 and / or S5 are performed multiple times and / or repeatedly, thereby resulting in accurate and reliable testing, especially blood pressure measurements, especially if the animal T or leg 2 moves during the test.

[0609] In particular, if in step S6 it is found that too many curve sections KA of one or more sensors 7 and / or too many curve sections in total are unusable or do not meet / satisfy the usability criteria, or too few of the curve sections are useful or meet / satisfy the usability criteria, it is possible to return to any of steps S1, S2, S3 and / or S4.

[0610] By going back to the previous step, it is possible, in particular, for the animal T to move during the examination or for the leg 2 to move during the examination. Measurement errors and / or movement artifacts arising from this can be compensated for by discarding unusable curves K or curve sections KA, in particular in connection with multiple presence detections and / or the selection of sensors 7 and / or multiple recordings of the heart rate curves KG and / or curves K. In particular, during or after the movement of the animal T or leg 2, it is possible to continue or continue the examination with one or more other sensors 7 or a different subset of sensors 7 than before the movement. The fact that the animal T can preferably move freely during the examination makes the examination very comfortable and stress-free for the animal T. This results in accurate and reliable examinations, in particular blood pressure measurement examinations.

[0611] Step S7 In step S7, an averaging is preferably performed based on a plurality of curve sections KA, in particular, only those curve sections KA that were not selected or discarded in step S6 are used in the averaging.

[0612] "Averaging" in this sense is in particular the determination of the average or mean course of a set of several curve sections KA or the average or mean course of the curve K during a heart beat.

[0613] During the averaging, in particular the curve mean value KM is determined. The averaging or determination of the curve mean value KM from the curve section KA is preferably carried out as already mentioned above in step S6. For the determination of the curve mean value KM, preferably a certain position or a certain time t i (KAj) For the value k i (KAj) are thus added. The result is preferably normalized. The curve mean value KM is therefore preferably calculated as i (KM) , k i (KM) ), especially k i (KM) is the position or time t i (KM) The value of the curve section KA at k i (K) Preferably, therefore,

number

[0614] In particular, in step S7, only those curve sections KA that were not selected or discarded in step S6 are used for determining one or more curve average values ​​KM. The method for determining the curve average value KM from the curve sections KA in this way is preferably identical in steps S6 and S7, but the curve average value KM determined in step S6 and the curve average value KM determined in step S7 differ in that different amounts of the curve sections KA are used or taken as a reference for determining the curve average value KM.

[0615] To determine the curve average value KM, the curve sections KA are preferably scaled and / or normalized, in particular so that all curve sections KA used to determine the curve average value KM have the same range of values, e.g. from -1 to 1 or similar values.

[0616] Preferably, in step S7, a resampling method is used, for which purpose preferably so-called subsamples are generated from the curve section KA.

[0617] In resampling techniques, statistical properties of a sample statistic, such as the mean, variance, degree of variance, or the like, can be determined based on the repeated drawing of subsamples from an initial sample.

[0618] The resampling method can be, for example, the bootstrap method, the jackknife method, the cross-validation, or a permutation test or a randomization test. However, particularly preferably, in the present invention, the resampling method is the bootstrap method. In the following, the bootstrap method is described in more detail.

[0619] When using the bootstrap method, the subsamples may also be referred to as bootstrap samples. In particular, the term "subsample" as used below in connection with the bootstrap method is also interchangeable with the term "bootstrap sample."

[0620] In the method, the initial sample is preferably formed by curve sections KA (possibly selected in step S6), in particular by one or more curves K and / or the entirety of the sensor 7. In particular, the initial sample comprises N curve sections KA, where N is therefore the number of curve sections KA in the initial sample.

[0621] The initial sample preferably only comprises the same curve K or curve section KA of the same sensor 7 .

[0622] The basic principle of the proposed bootstrap method is to create one or more subsamples with "sampling with replacement" from an initial sample, i.e., the curve section KA in this case.

[0623] The subsample is created by selecting M curve sections KA from the N curve sections KA of the initial sample.

[0624] The number M of curve sections KA of the sub-sample preferably corresponds to the number N of curve sections KA of the initial sample (M=N).

[0625] In particular, the selection of the M curve sections KA is random. The curve sections KA selected for the subsamples are preferably selected independently of each other. That is, the first of the M curve sections KA for generating the subsample is selected randomly from the N curve sections KA of the initial sample. Then, a further curve section KA is selected from the N curve sections KA of the initial sample. In particular, the further curve section KA is selected from the same set of curve sections KA as the first curve section KA. Thereafter, the further curve sections KA are selected in the same manner from the same set of curve sections KA until M curve sections KA are selected.

[0626] In other words, a subsample may contain the same curve section KA several times, since a curve section KA already selected once from the initial sample for generating the subsample is taken into account again when selecting a further curve section KA, which means that a curve section KA already selected once for generating the subsample may be selected again for a subsequent extraction of a curve section KA from the initial sample.

[0627] From the point of view of statistics or probability theory, this corresponds to "sampling with replacement", e.g., a curve section KA is "extracted" in turn from a set of curve sections KA and "put back" again before extracting the next curve section KA. Thus, the extraction of a curve section KA is always performed from the same set of curve sections KA. This means that the same curve section KA can be extracted several times during several extractions, and it is not possible not to extract a curve section KA at all.

[0628] Thus, in the present method, in the extreme case, it is in principle possible for one sub-sample to contain the same curve section KA M times, and it is also in principle possible for a sub-sample to never have the same curve section KA twice, such that the sub-sample corresponds exactly to the initial sample.

[0629] Typically, however, the sub-sample will include some curve sections KA of the initial sample multiple times, and some curve sections KA of the initial sample will not be included at all.

[0630] Preferably less than 1000, preferably less than 500, in particular less than 250, particularly preferably less than 100, very particularly preferably less than 75 and / or more than 10, preferably more than 30, particularly preferably about 50 subsamples are generated.

[0631] Typically, when using resampling or bootstrap methods, a large number of subsamples are generated, for example 1000 or more subsamples. In general, the accuracy and / or reliability of the sampling function can be improved by increasing the number of subsamples generated.

[0632] However, an increase in the number of subsamples also increases the amount of calculations required for the generation and evaluation of the curve K or curve section KA, which has a negative effect on the one hand on the energy consumption of the system used to perform the method, in particular the inspection device 1, and on the other hand on the computing power and / or computing time required to perform the method. It is therefore advantageous to keep the number of subsamples generated as small as possible.

[0633] In the context of the present invention it has been shown in a surprising manner that with the above mentioned relatively small number of subsamples it is already possible to achieve or determine sufficiently reliable and / or accurate results, in particular the curve characteristics M.

[0634] However, if the available computing power is very low, it may be possible and even preferable to generate fewer subsamples, for example less than 30, in particular as few as 15. Experiments have shown that meaningful results are already obtained with such a small number of subsamples.

[0635] The number of sub-samples created or to be created is preferably fixed. In particular, for each analysis of a curve K or a curve section KA, for example for curves K recorded in succession and / or measured with different sensors 7, the same number of sub-samples is generated.

[0636] In step S7, the curve mean value KM is preferably determined by the curve section KA of the initial specimen.

[0637] Preferably, as described above under step S6, curve mean values ​​KM of the curve sections KA are determined, where each curve section KA of the initial specimen is included exactly once in the calculation of the curve mean value KM.

[0638] Preferably, the curve mean value KM is also determined from the subsamples (each) in the same way as the initial sample. For this purpose, when calculating the curve mean value KM of the bootstrap sample, each of the M curve sections KA of the subsamples is taken into account exactly once. In this sense, the M curve sections KA of the subsamples represent different curve sections KA, even if some of the M curve sections KA should be identical due to the multiple selection of these curve sections KA from the initial sample when generating the subsamples.

[0639] In other words, the averaging based on a number of curve sections KA can be carried out taking into account in particular the sub-samples, in particular a curve mean value KM is determined for each of the sub-samples, preferably also for the initial sample.

[0640] As mentioned above, the initial specimen preferably only comprises curve sections KA which originate from the same curve K and / or which have been measured with the same sensor 7 and / or detector 6. However, it is also possible for the initial specimen to comprise curve sections KA which have been measured with different sensors 7 and / or detectors 6, in particular successively and / or shifted in time. This may be the case in particular if the animal T moves during the examination or recording of one or more curves K or if the leg 2 moves and / or if in the course of this one or more sensors 7 are selected again, in particular if a different subset of the sensors 7 is selected.

[0641] Essentially, it is advantageous to use resampling or bootstrap methods, but this is not essential.

[0642] Step S8 In step S8, preferably, a curve characteristic M is determined. The determination of the curve characteristic M is based in particular on the curve mean value KM determined in step S7.

[0643] Preferably, the curve characteristics M are thus determined on the basis of the curve sections KA and / or sub-samples.

[0644] For this purpose, a number of curve features M, preferably of the same type, can first be determined, of which one curve feature M is formed or selected at the end of step S8. This selected and / or formed curve feature M at the end of step S8 is called the curve feature M determined in step S8.

[0645] The determination of the curve characteristics M can be carried out separately for each curve K or for each sensor 7 and / or detector 6. In particular, for the determination of the curve characteristics M, only curve sections KA are taken into account which originate from the same curve K or from different curves K of the same sensor 7 and / or detector 6. However, other methods are also possible here.

[0646] Particularly preferably, a curve characteristic M is determined for the initial sample and for each subsample, in particular the curve K and / or the sensor 7 and / or the detector 6 .

[0647] It is therefore particularly preferred, in particular in step S7, to determine for each previously determined curve mean value KM the same curve features M. From these same curve features M, which in principle can take on different values ​​for each curve mean value KM, a curve feature mean value is calculated, preferably in particular the arithmetic mean of the curve features M.

[0648] The curve average value KM is preferably determined separately for each sensor 7 and / or detector 6, i.e. when calculating the curve average value preferably only curve sections KA measured with the same sensor 7 and / or detector 6 are used, so that the calculation of the curve feature average value is preferably performed separately for each sensor 7 and / or detector 6. In this way a curve feature average value is preferably available for each sensor 7 and / or detector 6. Preferably one of these curve feature average values ​​is selected (at the end of step S8), whereby in particular a sensor 7 and / or detector 6 is selected. This selected curve feature average value is called the curve feature M determined in step S8.

[0649] In principle, however, it is also possible to use curve sections KA of the curve K measured with different ones of the sensors 7 and / or detectors 6 to calculate the curve average value KM, where the curve sections KA measured with different sensors 7 and / or detectors 6 can be obtained from curves K measured simultaneously or alternatively or additionally from curves K measured successively and / or with a time delay.

[0650] The curve feature M is preferably a feature of the curve K or the curve section KA. The curve feature M is preferably a feature related to the pulse waveform delay PTT and / or blood pressure BP measurement, preferably a feature related to the pulse waveform delay PTT and / or blood pressure BP measurement. Alternatively or additionally, the curve feature M can correspond to the course of the curve average value. In particular, the curve feature M is a feature that can be used to measure the blood pressure BP.

[0651] In the following, some characteristics of the curve K or curve section KA are described by way of example, which can represent the curve characteristic M. However, further characteristics or features other than the characteristics described below can also represent the curve characteristic M.

[0652] Furthermore, the determination of the curve characteristic M is explained below with the aid of the curve mean value KM. In principle, however, it is also possible to determine the curve characteristic M directly using the curve sections KA, without the determination of the curve mean value KM or the curve mean value KM. In this case, the curve characteristic M is preferably determined separately for each curve section KA, and preferably the curve characteristic mean value is then determined.

[0653] Particularly preferably, the curve characteristic M is or corresponds to the pulse wave transit time PTT.

[0654] Preferably, the pulse transit time PTT corresponds to the time or position PM1 of an extreme value, in particular a maximum, of the curve mean value KM.

[0655] 12 shows an example of the curve mean value KM or its course. The curve mean value KM is preferably wavy. In particular, the curve mean value KM has two successive extreme values, in particular an (absolute) maximum and an (absolute) minimum, particularly preferably first the maximum and then the minimum.

[0656] The time or position PM1 of the maximum of the curve mean value KM preferably corresponds to the pulse transit time PTT. Therefore, the curve characteristic M is preferably the position PM1 of the maximum of the curve mean value KM.

[0657] In particular, the time or position PM1 of the maximum of the curve mean value KM corresponds to the pulse transit time PTT if the curve section start point corresponds to the time TH of the heartbeat. As explained at the beginning, if the curve K is sectioned based on the heartbeat curve KG at a time corresponding to the time TH of the heartbeat, the pulse transit time PTT can be read directly. Also, a correction can be made based on the time difference between the beginning of the curve and the heartbeat, or a subsequent intended blood pressure measurement can be made based on the relative pulse transit time PTT. Thus, the pulse transit time PTT does not necessarily have to be the absolute value of the time difference between the heartbeat and the arrival of the pulse wave at the measurement location, but may only (directly) correspond to it.

[0658] Alternatively or additionally to measuring the pulse transit time PTT, the pulse wave velocity can be determined. The pulse wave velocity is the quotient of the propagation distance of the pulse wave and the pulse transit time PTT required to travel this distance. In particular, the pulse wave velocity can be used instead of the pulse transit time PTT as a variable of the correlation function F to determine the blood pressure BP from the pulse transit time PTT and / or can be taken into account in the correlation function F in addition to the pulse transit time PTT.

[0659] Alternatively or additionally, the curve characteristic M is the time or position PM2 of the first and / or absolute minimum of the curve mean value KM.

[0660] Alternatively or additionally, the curve feature M is the time or position of the maximum negative slope of the curve mean value KM. In this case, the curve mean value KM is preferably first smoothed and the position of the curve feature M or maximum negative slope is determined using this smoothed curve mean value KM. Preferably, a smoothing filter such as a von-Hann window is used to smooth the curve mean value KM. The position of the maximum negative slope is between the absolute maximum and the absolute minimum in the illustrative example according to FIG. 12.

[0661] Alternatively or additionally, the absolute value of the maximum negative gradient is used (preferably instead of the position of the maximum negative gradient). In this case, the curve mean value KM is preferably first smoothed and this smoothed curve mean value KM is used to determine the curve feature M or the value or absolute value of the maximum negative gradient. Preferably, a smoothing filter such as a von-Hann window is used to smooth the curve mean value KM.

[0662] Alternatively or additionally, the curve characteristic M is the distance or time difference between the position PM1 of the absolute maximum and the position PM2 of the absolute minimum.

[0663] Alternatively or additionally, the curve characteristic M is the distance between the positions where the second derivative of the curve mean value KM has in each case a (local) maximum value, which corresponds to the distance between the positions where the curve mean value KM has the strongest curvature.

[0664] Alternatively or additionally, the curve characteristic M is the instantaneous harmonic phase shift, which is preferably determined as follows: a Fourier transform, preferably discrete, is applied to the curve mean value KM. The phase of the first harmonic vibration and the phase of the second harmonic vibration are then calculated, in particular by calculating the real and imaginary parts of the arctangent of the Fourier transform of the curve mean value KM. The difference between the phase of the first harmonic vibration and the phase of the second harmonic vibration is called the instantaneous harmonic phase shift.

[0665] Alternatively or additionally, the curve characteristic M is a section ratio. The section ratio is the ratio of the lengths of the different sections of the curve average value KM. For this purpose, first a first section and a second section of the curve average value KM are determined. Preferably, the first section starts at the location of the first zero of the first derivative of the curve average value KM and the first section ends at the location of the second zero of the first derivative of the curve average value KM. Preferably, the second section starts at the location of the first zero of the second derivative of the curve average value KM or at the location of the first maximum of the first derivative of the curve average value KM, respectively, and the second section ends at the location of the second zero of the first derivative of the curve average value KM. Preferably, a quotient of the length of the first section and the length of the second section is formed.

[0666] Alternatively or additionally, the curve characteristic M is the curvature of the curve K or of the curve section KA. This is particularly shown in FIG.

[0667] The curvilinearity of the curve K is in particular a measure of the extent to which the curve K deviates from a straight line in the curve section KA, in particular between the position PM1 of the first maximum and the position PM2 of the first minimum.

[0668] To determine the curvilinearity, the area of ​​the surface included by the curve K between the position PM1 of the first maximum and the position PM2 of the first minimum is preferably determined together with a straight line extending from the first maximum to the first minimum. The surface may consist of a number of disconnected sections, as shown in FIG. 15, here consisting of two sections, a single hatched section above the straight line and a double hatched section below the straight line. This enclosed surface is preferably normalized to the area of ​​a rectangle extending from the first maximum to the first minimum, or divided by the area of ​​which the first maximum and the first minimum of the curve K form two opposite corner points, as shown in particular in FIG. 15. Preferably, the line from the first maximum to the first minimum forms a diagonal of the rectangle. The sides of the rectangle run parallel to the x-axis and the y-axis.

[0669] Curvilinearity is therefore in particular the quotient between a first maximum and a first minimum, between the surface or area enclosed by a straight line and a curve extending from the first maximum to the first minimum, and the area of ​​a rectangle whose sides are parallel to the X-axis and the Y-axis and whose diagonal is formed by the straight line from the first maximum to the first minimum.

[0670] To determine the curvature, the area or surface above the line (single hatch in Fig. 15) may be counted with a positive sign, and the area or surface below the line (double hatch in Fig. 15) may be counted with a negative sign. In this case, for example, if the enclosed surfaces above and below the line each have the same area, the curvature will have a value of 0.

[0671] However, alternatively or additionally, it is also possible to determine an absolute curvilinearity, which is a measure of the deviation of the curve K from a straight line. To determine the absolute curvilinearity, preferably the absolute values ​​of the areas of all surfaces enclosed between the curve K and a straight line extending from the first maximum to the first minimum are added together to determine the surface or area enclosed between the straight line and the curve K. In other words, these areas are preferably entered with the same sign. Thus, preferably, when calculating the absolute curvilinearity, it is not taken into account whether a surface is above or below the straight line.

[0672] In particular, the determination of absolute curvature is preferred.

[0673] Alternatively or additionally, the curve characteristic M is the location or x-coordinate of the intersection of a horizontal or straight line passing through the first maximum with a slope of zero and a straight line or tangent passing through the point with the greatest slope between the first maximum and the first minimum, the tangent having the slope of the curve K or curve section KA at that point. This intersection is also called the tangent intersection for short.

[0674] In summary, therefore, the curve characteristic M is preferably one or a combination of some of the following values ​​of the curve mean value KM: Position PM1 of the first maximum value or pulse wave transit time (PTT) Position of the first minimum PM2 The distance between the position PM1 of the first maximum and the position PM2 of the first minimum Position of maximum negative slope The distance at which the second derivative has a maximum Maximum negative gradient value or absolute value Instantaneous harmonic phase shift Section ratio ·Curvature of curve K ·Tangential intersection

[0675] The curve feature M is preferably checked for plausibility, in particular whether it exceeds a specified or specifiable upper threshold and / or falls below a specified or specifiable lower threshold. This is explained in more detail above using the example of a pulse transit time PTT, which can only lie within a certain interval due to anatomical conditions. Similarly, for curve features M outside the pulse transit time PTT, a corresponding threshold can be specified, below or above which it is not plausible due to e.g. anatomical, biological and / or physical laws.

[0676] This plausibility check of the curve characteristics M includes in particular a check of the position PM1 of the first maximum and / or the plausibility of the determined pulse transit time PTT. If the position PM1 of the first maximum and / or the degree of dispersion of the pulse transit time PTT, in particular the interquartile range, reaches or exceeds a specified or specifiable upper threshold, the curve K or the sensor 7 and / or detector 6 from which the curve K was recorded is preferably discarded or not selected. For example, the threshold can be 5 ms or correspond to a degree of dispersion of the pulse transit time PTT, in particular the interquartile range, of 5 ms. In this way, the curve K or the sensor 7 and / or detector 6 from which a particularly inconsistent or non-uniform pulse transit time PTT can be determined on the basis of the curve section KA can be discarded or not selected.

[0677] Preferably, only a single one of the various curve characteristics M described above is determined, in particular for each curve average value KM, and preferably used for measuring the blood pressure BP. However, it is also possible to determine several curve characteristics M, in particular for each curve average value KM, and preferably used for measuring the blood pressure BP.

[0678] Preferably, a curve feature average value, in particular an arithmetic average of the curve feature M, is determined from the curve feature M of the initial sample and the sub-samples. The curve feature average value is therefore in particular an average, preferably an arithmetic average, of the curve feature M of the initial sample and the curve feature M of the sub-samples.

[0679] Particularly preferably, therefore, one of the curve characteristics M described above is determined for the initial sample as well as for each of the sub-samples, after which the mean value of these curve characteristics M is determined.

[0680] Preferably, the degree of dispersion, in particular the interquartile range, the standard deviation and / or the (empirical) variance, of the curve feature M is also determined. The degree of dispersion and / or the interquartile range, the standard deviation and / or the (empirical) variance are assigned to the curve feature mean value.

[0681] The degree of dispersion is in particular a measure that expresses the dispersion of the values, in this case in particular the dispersion of the curve characteristics M of the initial sample and the subsamples.

[0682] The interquartile range of a curve feature M is in particular the distance between the lower quartile (0.25 quartile) and the upper quartile (0.75 quartile). The interquartile range is therefore preferably the width of the interval in which the middle 50% of the determined curve feature M lies. In principle, however, other interquartile ranges can also be used.

[0683] As an alternative to the interquartile range, the measure of dispersion can also be the variance, in particular the empirical variance, and / or the standard deviation, however the use of the interquartile range has proven to be very robust and is therefore particularly advantageous.

[0684] Preferably, for each curve K or each sensor 7 and / or detector 6, the degree of dispersion assigned to this curve K or to this sensor 7 and / or detector 6 is determined separately. In particular, therefore, in determining the degree of dispersion, only the curve features M assigned to the initial sample and to subsamples of the same curve K or the same sensor 7 and / or detector 6 are taken into account.

[0685] The curve characteristic M is preferably determined separately for each sensor 7 and / or detector 6. In particular, only the curve mean value KM of a single sensor 7 and / or detector 6 is therefore used for the determination of the curve characteristic M.

[0686] As a result, for each sensor 7 and / or detector 6 the curve feature mean value assigned to this sensor 7 and / or detector 6 can therefore be determined separately.

[0687] In particular, the determined values ​​of the curve feature M and / or the curve feature average value of different sensors 7 and / or detectors 6 may differ.

[0688] Preferably, one of the curve characteristic average values ​​is then selected, in particular one of the sensors 7 and / or the detectors 6 and / or one of the curves K being thereby selected.

[0689] The selection of the curve feature mean value and / or the curve K and / or the sensor 7 and / or the detector 6 is preferably made based on or taking into account the degree of dispersion determined (in step S8), in particular the interquartile range, the (empirical) variance and / or the standard deviation.

[0690] One possibility for selecting the curve feature mean value and / or the curve K and / or the sensor 7 and / or the detector 6 is to select the curve feature mean value having the lowest degree of variance, in particular the lowest interquartile range, the lowest (empirical) variance and / or the lowest standard deviation.

[0691] A further possibility that has proven particularly advantageous in the context of the present invention is to use the amplitude of the maximum of the curve mean values ​​KM of the initial samples and / or subsamples in addition to the variance or interquartile range measurements to select the curve feature mean values.

[0692] In this case, it is preferable to proceed in particular for each sensor 7 and / or detector 6 individually as follows.

[0693] First, as described above, for each sub-sample and preferably for each initial sample, the curve feature M is determined, in particular the pulse wave transit time PTT and possibly one or more further curve features M. The curve feature M is then checked for validity separately for each sub-sample and preferably for the initial sample, as described above. If the curve feature M is valid or if all tested curve features M are valid, the respective sample is considered valid as a whole. Furthermore, the amplitude of the curve mean value KM of the respective sample is determined, in particular the value of the first maximum.

[0694] Furthermore, preferably, the interquartile range of the curve characteristics M, in particular the pulse transit times PTT, determined for the individual samples or sub-samples is determined ("IQR"). Furthermore, the mean or median of the amplitudes or values ​​of the first maxima of the curve mean values ​​KM of the individual samples or sub-samples is determined ("meanA"). Furthermore, the number of samples or sub-samples considered as plausible as a whole is determined ("num_S_plausible").

[0695] From these values ​​IQR, meanA and num_S_plausible, in particular for each detector 6 and / or sensor 7 for which the curve has been evaluated, the value L=IQR / meanA num_S_plausible" is preferably determined, i.e. the quotient of the interquartile range IQR and the product of the amplitude mean or median meanA and the number of valid samples num_S_plausible.

[0696] In this way, the value L can be assigned to each sensor 7 and / or detector 6 separately.

[0697] Preferably, the curve feature average value to which the smallest value L corresponds is then selected. This selection preferably corresponds to the selection of the sensor 7, since the curve feature average value has preferably been determined based on the curve K or curve section KA of a single sensor 7.

[0698] If the amplitude mean or median amplitude meanA is below a specified or specifiable threshold value, the curve K and / or the sensor 7 and / or detector 6 with which the curve K was measured are preferably discarded and / or not selected. The threshold value may for example have the value 0.2. As explained above, normalized curve sections are preferably used to determine the curve features M and / or the curve mean value KM, such that the amplitude or value of the first maximum in each curve section KA is 1. Thus, the amplitude mean or median amplitude meanA is a measure of how well the positions and / or courses or shapes of the first maxima of the curve sections KA match in (reasonable) samples, since if the positions and / or courses or shapes of the first maxima match perfectly, the amplitude mean or median amplitude meanA has the value 1, and the value is lower the more different the positions and / or courses or shapes of the first maxima are.

[0699] If the proportion of sub-samples for which the determination of the curve characteristic M results in a real pulse transit time PTT is below a specified or specifiable threshold, the curve K and / or the sensor 7 and / or the detector 6 from which the curve K was measured are preferably discarded and / or not selected. The real pulse transit time PTT is preferably a pulse transit time PTT that is above a lower threshold, e.g. 20 ms, and / or below an upper threshold, e.g. 175 ms, as explained above. The threshold for the proportion of sub-samples for which the determination of the curve characteristic M results in a real pulse transit time PTT can have, for example, a value of 0.8. In particular, this means that the curve K and / or the sensor 7 and / or the detector 6 are discarded and / or not selected if the proportion of sub-samples for which the determination of the curve characteristic M results in a real pulse transit time PTT is below 80%.

[0700] The curve feature mean value, preferably selected taking into account the degree of dispersion and / or the amplitude of the maximum or local maximum of the curve mean values ​​KM of the initial sample and / or sub-samples, is preferably the curve feature M determined in step S8.

[0701] As a result, the curve feature M, in particular the curve feature average value, used to measure the blood pressure BP is selected from a number of previously (preferably for different sensors 7) determined curve features M or curve feature average values ​​(in particular curve features M or curve feature average values ​​of the same type).

[0702] The selection can be made from curve features M or curve feature average values ​​each corresponding to one detector 6 and / or sensor 7. Alternatively or additionally, it is also possible to select from curve features M or curve feature average values ​​determined in connection with the previous step S7 by using subsamples.

[0703] Alternatively or additionally, it is possible to select from curve features M or curve feature average values ​​formed by combining curve sections KA of different sensors 7 and / or detectors 6. However, in the following it is also possible to determine and use only one curve feature M or curve feature average value.

[0704] The selection of the curve feature M or the curve feature average value in step S8 therefore constitutes in particular the selection of the sensor 7 and / or the detector 6. This is shown by way of example in Fig. 11. For the sake of clarity, only steps S3 and S8 are shown in Fig. 11, where the selection of the sensor 7 and / or the detector 6 is or can be performed. However, this does not mean that steps S4 to S7 are necessarily omitted. As shown in Fig. 11, preferably both the pre-selection of the sensor 7 and / or the detector 6 in step S3 and the selection of the curve K or the curve feature M or the curve feature average value in step S8 constitute the selection of the sensor 7 and / or the detector 6.

[0705] The selection of the sensor 7 is therefore preferably performed in several steps, in particular in steps S3 and S8. Preferably, the (first) selection of the sensor 7 (in particular in step S3) is performed before the optical examination, in particular photoplethysmography and / or recording of the curve K by the sensor device 4. More preferably (alternatively or additionally, in particular in step S3), the (further) selection of the sensor 7 is performed after the optical examination, in particular photoplethysmography and / or recording of the curve K by the sensor device 4. If in step S6 all curve sections KA of the curve K of the sensor 7 are to be discarded, this is preferably also the selection of the sensor 7, i.e. in this particular case only sensors 7 are selected whose curve sections KA have not been completely discarded.

[0706] Preferably, after the usefulness check of the curve sections KA described in step S6, if the remaining curve sections KA of the curve K and / or the number of the curve sections KA that are not discarded is equal to or less than a specified or specifiable threshold, the curve K and / or the sensor 7 and / or the detector 6 with which the curve K was recorded are discarded and / or not selected. The threshold can be, for example, 30, such that curves K with 30 or less useful curve sections KA are rejected and / or not selected. This step of rejecting and / or not selecting curves K with too few useful curve sections KA is not necessarily performed only in step S8, but can also be performed after step S6 and / or before step S7 or as a partial step of one of steps S6 and S7. Preferably, the averaging in step S7 is performed only on curves K with enough useful curve sections KA or for which the number of useful curve sections KA is equal to or greater than the above-mentioned threshold.

[0707] In particular, if in step S8 it turns out that the determined curve features M or some or all of the determined curve features M are inaccurate or unreliable, for example because the determined value L is too small or the degree of variance assigned to the curve features M is too large, it is possible to return to any of steps S1, S2, S3 and / or S4.

[0708] In particular, the return to the previous step allows the animal T to move during the test, the leg 2 to move during the test. Measurement errors and / or movement artifacts thus occurring can be compensated for by discarding unusable curves K or curve sections KA, in particular in connection with multiple presence detections and / or selections of sensors 7 and / or multiple recordings of the heart rate curves KG and / or curves K. In particular, during or after the movement of the animal T or leg 2, it is possible to continue or continue the test with one or more other sensors 7 or a different subset of sensors 7 than before the movement. The fact that the animal T can preferably move freely during the test makes the test very comfortable and stress-free for the animal T. This results in accurate and reliable tests, in particular blood pressure measurement tests.

[0709] Step S9 In step S9, preferably, in particular the systolic, diastolic and / or mean blood pressure BP is determined, in particular from the curve characteristics M determined in step S8. The blood pressure BP is determined using a correlation function F, preferably determined empirically.

[0710] The correlation function F therefore preferably represents a link between the curve features M, particularly determined in step S8, and the blood pressure BP, and assigns the blood pressure BP to the curve features M.

[0711] In particular, the correlation function F preferably does not explicitly take into account the arm or leg length between leg 2 and the heart of the animal T. In other words, preferably, the arm or leg length does not need to be explicitly determined.

[0712] Rather, in the context of the present invention, it has been surprisingly shown that the same correlation function F can be used for different animals T of the same species or breed, in particular different domestic cats, leading to meaningful results. However, preferably, different correlation functions F are used for different animal species or breeds.

[0713] The correlation function F is preferably determined by a study in which the blood pressure BP is determined by an established method for measuring the blood pressure BP and is assigned to the curve characteristics M determined by the method according to the invention. The correlation function F is then determined by adapting the parameters of the correlation function F such that the blood pressure BP determined by the method according to the invention corresponds at least substantially to the blood pressure BP determined by the established method.

[0714] The correlation function F is preferably a scalar field that depends on at least two variables.

[0715] Preferably, the curve characteristics M, and in particular the pulse transit time PTT, constitute the variables of the correlation function F.

[0716] Preferably, in addition to the curve characteristics M, in particular the pulse transit time PTT, the heart rate constitutes a variable of the correlation function F. The heart rate represents the number of heart beats in a certain time interval and is preferably determined from the heart rate curve, in particular from the distance of the QRS complex or the R peak.

[0717] Therefore, the correlation function F can take the following functional form, for example: F(x,y)=a x + b y + c where x represents the curve characteristic M, in particular the pulse wave transit time PTT and / or the position PM1 of the first maximum, y represents the heart rate and a, b, c represent the parameters to be determined.

[0718] Furthermore, the correlation function F can depend on further variables. Particularly preferably, the distance between the position PM1 of the first maximum and the position PM2 of the first minimum of the curve section KA or the curve mean value KM constitutes a further variable of the correlation function F.

[0719] Therefore, the correlation function F can also take the functional form: F(x,y)=a x + b y + c z + d where x denotes the curve feature M, in particular the pulse wave transit time PTT and / or the position PM1 of the first maximum, y denotes the heart rate, z denotes the distance between the position PM1 of the first maximum and the position PM2 of the first minimum, and a, b, c and d denote the parameters to be determined.

[0720] Furthermore, the correlation function F is preferably a non-linear function. The correlation function F may therefore depend non-linearly on the curve characteristics M and / or on the heart rate, and in particular therefore on the higher order terms in x, y and / or z (x 2 , x 3 , y 2 , y 3 , z 2 , z 3 , etc.).

[0721] Furthermore, the correlation function F can depend on further variables or on more than the three variables x, y, z.

[0722] In particular, in the measurement of the blood pressure BP or as a variable of the correlation function F, the curvature of the curve K can be taken into account instead of or in addition to the quantities already mentioned.

[0723] In particular, in an animal T of the feline subfamily, such as a cat, it has been shown that the curvature of the curve K changes due to a change in blood pressure BP instead of or in addition to the pulse wave transit time PTT. In other words, in some cases, the blood pressure BP may be reflected in the curvature of the curve K even if there is no particular change in the blood pressure BP that brings about a change in the pulse wave transit time PTT, and therefore, in determining the correlation function F or the blood pressure BP, it may be important to take into account the curvature of the curve K instead of or in addition to the pulse wave transit time PTT.

[0724] Regarding various correlation functions F for blood pressure measurement from pulse wave transit time and / or heart rate, see M. Sharma et al., Cuff-Less and Continuous Blood pressure Monitoring: A Methodological Review, Technologies 2017, 5(2), 21. The correlation function F of the present invention can have a functional form that follows one of the mathematical models described in Chapters 3 and 4, in particular one of equations (6) to (10) or follows Table 3.

[0725] In the correlation function F, especially in its parameters, various other characteristics of the animal T, such as size, weight, gender, age, and / or the color and / or pigment of leg 2 or the hoof of leg 2, can be alternatively or additionally considered.

[0726] In principle, the correlation function F can also depend on the anatomical particularities of each animal T. For example, the size of the animal T or a measure corresponding to the size of the animal T, such as body length, shoulder height, leg or arm length, or any other parameter corresponding to the distance between the heart and leg 2, can be made to be considered in the correlation function F in the form of any of the parameters a, b, c, or d. In many cases, since this can lead to a sufficiently accurate conclusion about the distance between the heart and leg 2, the preferred parameter in this context can be the weight of the animal T. In this regard, the correlation function F can have the weight of the animal T as a parameter, or the weight of the animal T can be considered by one of the parameters a, b, c, d.

[0727] Complementarily, parameters corresponding to body fat percentage such as bioimpedance can also be considered. Each measurement can be performed using the electrode 15 and / or the scale 18 for measuring the heart rate curve KG. In particular, the combination of bioimpedance and the weight of the animal T is considered in the correlation function F by implicit or practical conclusions about the anatomical particularities of the animal T regarding the distance between the heart and leg 2, enabling the blood pressure BP to be measured more reliably from the curve feature M.

[0728] Taking into account characteristics of the animal T, such as height, weight, body fat percentage or the like, is preferably done in the form of parameters (a, b, c, d) instead of variables (x, y, z) in the correlation function F. In other words, each characteristic does not enter the correlation function F directly as a variable, but preferably only as a parameter or indirectly.

[0729] Preferably, the properties of the animal T are taken into account in the form of discrete parameters. Discrete parameters in this sense are in particular parameters that can take on a certain number of different values, for example 2, 3 or 4 different values. This makes it possible to take into account the properties of the examined animal in the correlation function F without explicitly including this property as a variable of the correlation function F.

[0730] In particular, animals T can be classified into different groups according to a characteristic such as height, weight, body fat percentage or the like, where this characteristic is taken into account in the correlation function F by means of a discrete parameter, with each different value of the parameter corresponding to one of the different groups.

[0731] The classification of the animal T and the associated selection between the possible discrete parameter values ​​may be performed automatically. Alternatively or additionally, the classification of the animal T may be performed by manual input or the like, in particular by input at the testing device 1 and / or before the test or measurement is performed.

[0732] Particularly preferably, in one of the parameters of the correlation function F, in particular the parameter a linked to the curve characteristic M, the size and / or weight of the animal T, in particular a cat, is taken into account. Preferably, this is done in the form of a binary parameter. A binary parameter is in particular a parameter which can take only two different values. In other words, preferably two different values ​​a1 and a2 are provided for the parameter a, where for large and / or heavy animals T the value a1 is used as parameter a in the correlation function F and for small and / or light animals T the value a2 is used as parameter a in the correlation function F. The subdivision into large and / or heavy animals T and small and / or light animals T is preferably performed by a limit value, above which the animal T is classified as a large and / or heavy animal and below which the animal T is classified as a small and / or light animal. Here, the limit value is preferably a value corresponding to the size and / or weight of the animal T, such as, for example, the length of the arms and / or legs, the height of the shoulders, the total length of the animal T, the weight of the animal T or similar.

[0733] Preferably, the systolic and / or diastolic blood pressures BP are determined. For the systolic and diastolic blood pressures BP, preferably different correlation functions F are used, the different correlation functions F preferably having the same functional form or depending on the same variables and / or only differing in the values ​​of the parameters (a, b, c, d).

[0734] It is expressly indicated that the method and / or the examination device according to the invention can also be used in particular for diastolic blood pressure measurements, which has been shown in studies during the development of the invention.

[0735] The blood pressure BP determined from the curve characteristic M by the correlation function F can be output or transmitted, for example, to an external device 23, for example a mobile terminal, a smartphone, a server or a database or the like. Alternatively or additionally, the determined blood pressure BP can be displayed by means of the examination apparatus 1, in particular the display device 19.

[0736] overview In FIG. 13 the proposed method or several steps of the proposed method are again graphically summarized.

[0737] Preferably, a heart rate curve KG is recorded. In particular, the heart rate curve KG is an electrocardiogram and / or the heart rate curve KG is recorded using the electrodes 15 of the examination device 1.

[0738] Preferably, a check of the usefulness of the heart rate curve KG is performed before any further measurements and / or evaluations. In particular, it is checked here whether heart beats can be reliably identified in the heart rate curve KG and / or whether the heart rate curve KG contains useful information. The check of the usefulness of the heart rate curve KG is preferably performed on the basis of heart rate curves KG of a few seconds in length and / or on the basis of heart rate curves KG having or representing several heart beats, for example 5 to 10 heart beats.

[0739] If the heart rate curve KG is not useful or does not meet / conform to the criteria of the usefulness check, it is advisable to record a new heart rate curve KG, which is represented by the arrow P1 in FIG.

[0740] Furthermore, a curve K containing information about the arterial blood flow BF is preferably recorded. This is done in particular by means of the sensor device 4. The curve K is preferably recorded simultaneously with the heart rate curve KG.

[0741] Preferably, the usefulness of the curve K is checked. If the curve K is not useful, a new curve K is preferably recorded. This is represented by the arrow P2 in Fig. 13. Alternatively or additionally, a new heart rate curve KG can be recorded or the measurement of the heart rate curve KG and / or the curve K can be started again. This is represented in particular by the arrow P3.

[0742] The curve K is then preferably evaluated taking into account information, in particular from the heart rate curve KG. For this purpose, the curve K is preferably cut into curve sections KA at times TH which are determined on the basis of the heart rate curve KG and which correspond in particular to a position from the QRS complex thereto, preferably the R peak.

[0743] The blood pressure BP is preferably determined from the heart rate curve KG and / or from the curve K. This is preferably done by determining at least one curve feature M from the curve K and determining the blood pressure BP from the curve feature M, preferably by means of an empirical correlation function F.

[0744] The correlation function F may be preset and may in particular be stored in a storage medium 26 of the inspection apparatus 1 or in the external device 23 .

[0745] The blood pressure BP can be output in particular by the display device 19 and / or by the external device 23.

[0746] Further aspects of the invention which can be realised independently or in combination with the above mentioned aspects and features are in particular the following:

[0747] 1. A method for the medical examination, in particular the measurement of blood pressure BP, of an animal T, in particular an animal T having a leg 2, particularly preferably an animal T of the feline subfamily, in which a curve K, in particular a photoplethysmogram, containing information about the arterial blood flow BF of the animal T is recorded, A method according to claim 1, characterized in that the curve K is cut into a plurality of curve sections KA, each curve section KA corresponding to a heart beat.

[0748] 2. The method according to aspect 1, characterized in that for the evaluation, averaging is performed based on a plurality of curve sections KA and / or a curve mean value KM is determined from a plurality of curve sections KA.

[0749] 3. The method according to aspect 1 or 2, characterized in that a subset of the curve sections KA is selected for evaluation, in particular one or more curve sections KA being discarded.

[0750] 4. The method according to any one of aspects 1 to 3, characterized in that a resampling method, in particular a bootstrap method, is used for the evaluation and a subsample, in particular a bootstrap sample, is generated from the curve section KA.

[0751] 5. The method according to aspect 4, characterized in that the sub-sample has a curve section KA of less than 200, preferably less than 100, in particular less than 60 and / or more than 15, preferably more than 30, particularly preferably about 45.

[0752] 6. The method according to aspect 4 or 5, characterized in that less than 1000, preferably less than 500, in particular less than 250, particularly preferably less than 100, very particularly preferably less than 75 and / or more than 10, preferably more than 30, particularly preferably about 50 bootstrap samples are generated.

[0753] 7. A method according to any one of aspects 1 to 6, wherein one or more curve features M, in particular the pulse wave transit time PTT and / or values ​​corresponding thereto or correlating therewith, are determined from the curve sections KA and / or sub-samples.

[0754] 8. The method according to aspect 7, characterized in that for each sub-sample a curve characteristic M, in particular a pulse wave transit time PTT, is determined and / or a mean value and / or a curve characteristic mean value is calculated from the curve characteristic M, in particular a pulse wave transit time PTT, in particular for each sub-sample and preferably for the initial sample.

[0755] 9. The method according to aspect 7 or 8, characterized in that the degree of dispersion of the curve feature M and / or the curve feature mean value, in particular the pulse wave transit time PTT, in particular the interquartile range, is determined.

[0756] 10. The method according to any one of aspects 1 to 9, characterized in that a number of curves K are recorded simultaneously and / or successively, the degree of dispersion is determined for each of the curves K, and based on the degree of dispersion, one of the curves K is selected for further evaluation, in particular for measuring a blood pressure BP.

[0757] 11. The method according to any one of aspects 7 to 10, characterized in that the blood pressure BP is measured by a correlation function F, preferably empirically determined from the curve characteristics M, in particular the pulse wave transit time PTT.

[0758] 12. A procedure according to any one of aspects 1 to 11, characterized in that the heart rate curve KG is recorded simultaneously with the curve K.

[0759] 13. The method according to embodiment 12, characterized in that the curve K is cut into curve sections KA by information from the heart rate curve KG.

[0760] 14. The method according to aspect 12 or 13, characterized in that the time TH of the heartbeat is determined using the QRS complex of the heartbeat curve KG, in particular the position of the R peak of the QRS complex, and preferably the curve K is cut into curve sections KA at the time TH determined using the QRS complex.

[0761] 15. A method according to any one of aspects 12 to 14, characterized in that the usefulness of the heart rate curve KG is automatically checked, and if the heart rate curve KG is not useful, the heart rate curve KG and the curve K are discarded, and a new heart rate curve KG and a new curve K are recorded.

[0762] 16. A method according to any one of aspects 1 to 15, characterized in that the curve K or its curve section KA is automatically checked for usefulness, and if the curve K is not useful, the curve K is discarded and a new curve K is recorded.

[0763] 17. The method according to any one of aspects 1 to 16, characterized in that a plurality of curves K are recorded and curve sections KA from different ones of the recorded plurality of curves K are used for evaluation.

[0764] 18. A method for medical examination, in particular for measuring the blood pressure BP, of an animal T, in particular an animal T having a leg 2, in particular preferably of the feline subfamily, preferably when the method is designed according to one of the above-mentioned embodiments, in which the arterial blood flow BF of the animal T is optically examined, in particular photoplethysmography, by means of a sensor device 4, the sensor means 4 having one or more emitters 5 of the same type for emitting electromagnetic radiation R and a plurality of detectors 6 of the same type for detecting the radiation emitted by the emitters 5, such that the emitters 5 and the detectors 6 form a plurality of sensors 7 of the same type, A sensor 7 or a subset of sensors 7 is selected; A method comprising:

[0765] 19. The method according to embodiment 18, characterized in that the sensors 7 each have a sensor area 11, the sensor areas 11 of the sensors 7 each are in different positions and together form a sensing area, different sub-areas of the sensing area are sensed in each sensor 7, and a specific sub-area of ​​the sensing area is selected for the medical test.

[0766] 20. A method according to aspect 18 or 19, characterized in that a presence determination is made, in particular checking whether the animal T or leg 2 is located on an inspection device 1 and / or above a sensor device used to carry out the method so that an optical inspection can be carried out by the inspection device 1 and / or the sensor device 4.

[0767] 21. A method according to any one of aspects 18 to 20, characterized in that a position determination is performed, in particular checking and / or determining over which sensor 7 of the sensor device 4 the leg 2, in particular the paw pad, is located and / or over which sensor 7 an optical inspection can be performed.

[0768] 22. A method according to any one of aspects 18 to 21, characterized in that it is checked whether the leg 2 is located in the sensor area 11 of the sensor 7, and for this check the signal S measured by the sensor 7 is analyzed, in particular checking whether the absolute signal strength exceeds or falls below a threshold value.

[0769] 23. A method according to any one of aspects 18 to 22, characterized in that the selection of the sensor 7 or the subset of sensors 7 is performed before performing an optical inspection using the sensor device 4 and / or before the curve K is recorded with the sensor device 4.

[0770] 24. A method according to any one of aspects 18 to 23, characterized in that the selection of the sensor 7 or the subset of sensors 7 is made after carrying out an optical inspection using the sensor device and / or after recording the curve K with the sensor device 4, in particular by selecting a subset of the curves K recorded with different sensors 7.

[0771] 25. A method according to any one of aspects 1 to 24, characterized in that a curve K, in particular a photoplethysmogram, containing information about the arterial blood flow BF is recorded by a sensor 7, at least one of the curves K is selected for evaluation, preferably the quality of the recorded curves K is determined by statistical analysis, and the curve K having the highest quality is selected for evaluation.

[0772] 26. A method according to any one of the preceding aspects, characterized in that the curve K selected for evaluation is divided into curve sections KA, and a subset of the curve sections KA of the selected curve K is used for evaluation.

[0773] 27. A method according to any one of aspects 1 to 26, characterized in that a plurality of curves K are recorded in succession, the curves K are divided into curve sections KA, and the curve sections KA of the curves K recorded in succession by the same sensor 7 are used for evaluation.

[0774] 28. A method according to any one of aspects 1 to 27, characterized in that a number of curves K are recorded simultaneously, the curves K are divided into curve sections KA, and the curve sections KA of the curves K recorded simultaneously by different sensors 7 are used for evaluation.

[0775] 29. A method according to any one of aspects 1 to 28, characterized in that the curve characteristic M and / or the curve characteristic average value, in particular the pulse wave transit time PTT, or a value corresponding thereto or correlated thereto, is determined by means of the curve K.

[0776] 30. A method according to any one of aspects 1 to 29, characterized in that a plurality of different curve features M and / or curve feature average values ​​are determined according to the curve K, preferably the different curve features M and / or curve feature average values ​​being or representing different features of the same curve K.

[0777] 31. The method according to aspect 29 or 30, characterized in that the blood pressure BP is measured from the curve characteristic M and / or the curve characteristic average value, in particular the pulse transit time PTT, by means of a correlation function F, preferably empirically determined.

[0778] 32. A method according to any one of aspects 1 to 31, characterized in that the curve K is divided into curve sections KA, each of which corresponds to a heart beat, and an average value is calculated from a plurality of curve sections KA, preferably a heart beat curve KG is recorded simultaneously with the curve K, and the curve K is divided into curve sections KA by information from the heart beat curve KG.

[0779] 33. The method according to any one of aspects 1 to 32, wherein a diastolic blood pressure measurement, BP, is determined.

[0780] 34. An examination device 1 for medical examination, in particular for measuring blood pressure BP, of an animal T, in particular an animal T having a leg 2, particularly preferably an animal T of the feline subfamily, a sensor device 4 for optical examination of the arterial blood flow BF of an animal T, in particular for performing photoplethysmography, In an inspection device 1, the sensor means 4 comprises one or more emitters 5 of the same type for emitting electromagnetic radiation R and a plurality of detectors 6 of the same type for detecting the radiation R emitted by the emitters 5, such that the emitters 5 and the detectors 6 form a plurality of sensors 7 of the same type, An inspection device 1, characterized in that it comprises a control device 25 designed to select a sensor 7 or a subset of sensors 7.

[0781] 35. The inspection device described in embodiment 34, wherein each of the sensors 7 has multiple emitters 5.

[0782] 36. The inspection device according to aspect 34 or 35, wherein each emitter 5 is part of a plurality of sensors 7.

[0783] 37. An inspection device as described in any one of aspects 34 to 36, characterized in that each sensor 7 has a sensor area 11, the sensor areas 11 of the sensors 7 are each located at a different position and together form a sensing area, each sensor area 11 forming a different sub-area of ​​the sensing area, and the different sub-areas of the sensing area can be selected by a controller or control device 25.

[0784] 38. An examination device described in any one of aspects 34 to 37, wherein the examination device 1 and / or the control device 25 are designed to perform a method described in any one of aspects 1 to 33, and the examination device 1 and / or the control device 25 are designed to measure diastolic blood pressure.

[0785] 39. An examination device 1 for performing medical examinations, in particular photoplethysmography, comprising: Preferably, the inspection device 1 is designed according to any one of aspects 35 to 38, at least one emitter 5 for emitting electromagnetic radiation R and at least one detector 6 for detecting the radiation R emitted by the emitter 5, An inspection device, characterized in that the inspection device 1 comprises means adapted to carry out the steps of the method according to any one of aspects 1 to 33.

[0786] 40. A computer program comprising instructions that, when executed, cause the inspection device 1 to perform the steps of the method according to any one of aspects 34 to ...

Claims

1. A method for measuring blood pressure in an animal (T) executed by a processor (P), comprising: A curve (K) containing information about the arterial blood flow of the animal (T) is recorded, the processor (P) divides the curve (K) into a plurality of curve sections (KA) such that each curve section (KA) corresponds to a heart beat; said processor (P) uses a resampling method for the evaluation of said recorded curve (K), in which said processor (P) determines statistical properties of a sample statistic based on repeated drawing of sub-samples from an initial sample, said processor (P) generating said sub-samples from said curve section (KA); A method comprising:

2. 2. A method according to claim 1, characterized in that for the evaluation of the recorded curve (K), the processor (P) performs an averaging based on the curve sections (KA).

3. 3. A method according to claim 1 or 2, characterized in that the processor (P) selects a subset of the curve sections (KA) for the evaluation of the recorded curve (K).

4. Method according to any one of claims 1 to 3, characterized in that the processor (P) determines the length of the curve section (KA) on the basis of an average heart rate.

5. 5. The method according to claim 1, wherein the sub-sample has less than 200 and / or more than 15 curve sections (KA).

6. The method according to any one of claims 1 to 5, characterized in that less than 1000 and / or more than 10 subsamples are generated.

7. Method according to any one of the preceding claims, characterized in that said processor (P) determines curve characteristics (M) from said curve sections (KA) and / or sub-samples.

8. 8. The method of claim 7, wherein the processor (P) determines a degree of variance of the curve features (M).

9. 9. The method according to claim 7 or 8, characterized in that the processor (P) measures the blood pressure (BP) by a correlation function (F) based on the curve characteristics (M).

10. The method according to any one of claims 1 to 9, wherein the processor (P) records a heart rate curve (KG) simultaneously with the curve (K).

11. 11. The method according to claim 10, characterized in that the processor (P) uses the QRS complexes of the heart rate curve (KG) to determine the time (TH) of the heart beat.

12. The processor (P) checks the usefulness of the heart rate curve (KG) by checking one or more criteria, the following criteria being: the peak-to-peak amplitude of the cardiogram (KG) is equal to or greater than a specified or specifiable threshold; a quotient between an integral value of a power density spectrum in a first section of the heart rate curve (KG) and an integral value of a power density spectrum in a second section of the heart rate curve (KG) is greater than or equal to a lower threshold and / or less than or equal to an upper threshold; the kurtosis and / or skewness of the amplitude distribution function of the cardiogram (KG) is equal to or greater than a specified or specifiable threshold; the minimum and / or mean amplitude of the peaks of the Pan-Tompkins plot of said heart rate curve (KG) is equal to or greater than a specified or specifiable threshold; the minimum, maximum and / or average distance of the peaks of the Pan-Tompkins plot of said heart rate curve (KG) is greater than or equal to a lower threshold and / or less than or equal to an upper threshold; the percentage of time that the heart rate curve (KG) is saturated is below a specified or specifiable threshold; The cardiogram (KG) is deemed useful if at least one of the following conditions is met:

12. The method according to claim 10 or 11, characterized in that if the processor (P) determines that the heart rate curve (KG) is not useful, the processor (P) discards the heart rate curve (KG) and the curve (K) and the processor (P) records a new heart rate curve (KG) and a new curve (K).

13. 13. The method according to any one of claims 1 to 12, characterized in that the processor (P) records a plurality of curves (K) and the processor (P) uses curve sections (KA) from different ones of the recorded plurality of curves (K) for the evaluation of the recorded curve (K).

14. 14. An examination device (1) for performing blood pressure measurements, comprising at least one emitter (5) for emitting electromagnetic radiation (R) and at least one detector (6) for detecting the radiation (R) emitted by the emitter (5), the examination device (1) having the processor (P) adapted to perform the steps of the method according to any one of claims 1 to 13.

15. A computer program comprising instructions which, when executed, cause an inspection device (1) according to claim 14 to carry out the steps of the method according to any one of claims 1 to 13.

16. A computer-readable storage medium (26) having stored thereon a computer program as claimed in claim 15 or having stored thereon instructions which, when executed, cause an inspection device (1) as claimed in claim 14 to carry out the steps of the method as claimed in any one of claims 1 to 13.

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