DEVICE, SYSTEM, AND METHOD FOR DETERMINING VITAL SIGNS OF A SUBJECT - Patent application

Abstract

The present invention relates to a device 100 for determining a subject's vital signs through the use of PPG. The device comprises a processing unit 110 configured to acquire a plurality of first detection signals from a plurality of measurement spots 30 on a skin area 12 of the subject illuminated with one or more illumination spots 20, where the first detection signals are derived from electromagnetic radiation 90 entering the skin area 12 at one or more illumination spots 20 and exiting the skin area 12 at the plurality of measurement spots 30. The processing unit 110 further acquires 3D image information 130 of the skin area 12, thereby enabling the determination of actual spot distances 15 between the measurement spots 30 and the illumination spots 20, respectively. This information can be used to more accurately interpret the PPG signals, since without 3D image information, the projection distance can only be determined when the skin surface is tilted. Additionally, this allows the PPG signals derived from a homogeneous skin area to be averaged to improve PPG signal strength and reduce noise. A system 500 including such a device and a corresponding method is further described.

Description

[Technical field]

[0001] The present invention relates to devices, systems and methods for determining vital signs of a subject. [Background technology]

[0002] For example, a person's vital signs, such as heart rate, respiratory rate, or arterial oxygen saturation, serve as indicators of a person's current condition and as strong predictors of serious medical events. For this reason, vital signs are widely monitored in inpatient and outpatient care settings, at home, or in further health, leisure, and fitness settings.

[0003] One technique for measuring vital signs is plethysmography (PPG), which generally refers to the measurement of volumetric changes in an organ or body part, and in particular the detection of volumetric changes due to cardiovascular pulse waves that move through a subject's body with each heartbeat.

[0004] More specifically, PPG is an optical measurement technique that evaluates the time-varying variations in light reflectance or transmittance of a region or volume of interest, based on the principle that blood absorbs more light than the surrounding tissue. Thus, changes in blood volume with each heartbeat affect the transmittance or reflectance accordingly. In addition to information about the heart rate, PPG waveforms can contain information resulting from further physiological phenomena such as respiration. By evaluating the transmittance and / or reflectance at different wavelengths (usually red and infrared), the blood oxygen saturation, SpO2, can also be determined.

[0005] Recently, non-contact remote PPG (rPPG) devices for unobtrusive measurements have been introduced. Remote PPG utilizes a light source, or typically a radiation source, placed away from the subject. Similarly, a detector, e.g. a camera or a photodetector, is also placed away from the subject of interest. Non-contact camera-based PPG, as a special kind of non-contact remote PPG, typically uses wide-field (uniform) illumination and detection. Therefore, this technique is referred to below as "wide-field PPG". The PPG signal intensity in wide-field PPG is typically very small (less than 1% of the modulation). This is because most of the backscattered / transmitted light travels only a very short distance through the subject's skin. This very small signal intensity is a significant drawback of non-contact camera-based PPG compared to conventional contact PPG probes (by a factor of at least 10-100). In many anatomical locations, wide-field PPG signals cannot be practically measured (e.g. on the legs or arms), but the use of contact sensors makes this possible.

[0006] Another possibility of non-contact camera-based PPG, based on the use of illumination patterns or on the use of a single spot, for example created by a laser, is proposed here and is hereafter called "radial PPG". The advantage of radial PPG is that it is possible to measure light that has traveled a longer distance through the skin than in the case of wide-field PPG. As a result, a significantly larger PPG modulation depth can be measured, which overcomes the disadvantages of the usual wide-field camera-based PPG discussed above. However, the disadvantage is that the spatial resolution is reduced compared to wide-field PPG. Another problem arising from radial PPG is that if only one illumination spot is evaluated, only a few camera pixels can transmit a signal in the dynamic range of the camera. Furthermore, the scale of the image is not calibrated, which does not allow a meaningful evaluation of the radial PPG signal.

[0007] US2018 / 000359A1 discloses a biological information detection device including a light source, an image capture device, and one or more computational circuits. The light source projects dots formed by light onto a target including a living organism. The image capture device includes photodetector cells and generates an image signal representing an image of the target onto which the dots are projected. The one or more computational circuits use the image signal to detect a portion in the image corresponding to at least a portion of the living organism, and use the image signal of the portion to calculate biological information of the living organism.

[0008] US 2017 / 095170 A1 relates to a device, a system and a method for obtaining vital signs related information of a living organism. The proposed device comprises an input unit for receiving an input signal generated from light reflected from a skin area of ​​a living organism and received in at least one wavelength interval, said input signal being representative of vital signs related information from which a vital sign of the living organism is derived, a processing unit for processing the input signal and deriving from said input signal vital signs related information of the living organism, an orientation estimation unit for estimating an orientation of the skin area, and a processing unit for controlling a lighting unit for illuminating the skin area with light for illuminating the skin area based on the estimated orientation of the skin area and / or for controlling the processing unit to derive vital signs related information from the input signal obtained during a selected time interval based on the estimated orientation of the skin area. Summary of the Invention [Problem to be solved by the invention]

[0009] Based on different problems arising from conventional radial PPG, it is an object of the present invention to provide more accurate devices, methods and systems for determining a subject's vital signs. [Means for solving the problem]

[0010] In a first aspect of the present invention, a device for determining a subject's vital signs is presented, comprising: - obtaining a plurality of first detection signals from a plurality of measurement spots on a skin area of ​​the subject illuminated with one or more illumination spots, where the plurality of first detection signals are derived from electromagnetic radiation entering the skin area at the one or more illumination spots and exiting the skin area at the plurality of measurement spots; - Obtain 3D image information of the skin area; - determining, for the plurality of first detection signals, respective spot distances between the respective measurement spots and the illumination spot based on the acquired 3D image information of the skin area; - assigning a plurality of first detection signals to respective spot distances and illumination spots for which respective spot distances are determined; - a processing unit configured to average first detection signals assigned to the same illumination spot and respective spot distances smaller than a threshold distance value to obtain an averaged first detection signal and to determine an averaged vital sign from the averaged first detection signals or to determine a vital sign from first detection signals assigned to the same illumination spot and respective spot distances smaller than a threshold distance value and to average the vital signs to obtain an averaged vital sign.

[0011] According to another aspect of the present invention, a system for determining vital signs of a subject is presented, which comprises, in addition to the above-mentioned device, an illumination unit configured to emit electromagnetic radiation to illuminate a skin area of ​​the subject with one or more illumination spots, and a camera configured to record an image of the detected electromagnetic radiation illuminated with the one or more illumination spots and reflected from the skin area, and to derive a plurality of first detection signals from the recorded image.

[0012] In yet another aspect of the present invention, there is provided a non-transitory computer readable recording medium storing a computer program product which, when executed by a processor, causes a computer to perform the methods disclosed herein, as well as a corresponding method and a computer program comprising program code means which, when executed on a computer, causes the computer to perform the steps of the methods disclosed herein.

[0013] Preferred embodiments of the invention are defined in the dependent claims. It is to be understood that the claimed methods, systems, computer programs and media have preferred embodiments similar and / or identical to the claimed devices, in particular as defined in the dependent claims and as disclosed herein.

[0014] The present invention is based on the idea that radial PPG measurement using illumination with one or more illumination spots (e.g. emitted by a laser) requires knowledge of the actual spot distance of the measurement spot from which the PPG signal is derived relative to the illumination spot on the skin area. In contrast to wide-field PPG, where the subject's skin is uniformly illuminated and the wide-field PPG signal intensity is independent of the position on the skin and the local orientation of the skin, the radial PPG signal can be strongly dependent on both the position (relative to the illuminated area) and the orientation of the skin surface.

[0015] If the orientation of the skin surface is perpendicular to the illumination direction and perpendicular to the recording camera, it is relatively easy to measure the absolute spot distance with the camera, since the lateral distance in the image can be easily calibrated (e.g. by a known angular distance between the illumination dot and the measurement dot). In the case of curved skin areas, a correction of the projection is necessary and the determination of the actual spot distance is much more complicated. The orientation of the skin surface perpendicular to the recording camera shall be understood in the context to mean that the skin surface faces its entire surface towards the recording camera.

[0016] For this purpose, the processing unit of the claimed device is configured to acquire 3D image information of the skin area. This allows for determining the respective spot distances between the respective measurement spots and the illumination spot based on the acquired 3D image information of the skin area for a plurality of first detection signals derived from electromagnetic radiation from a plurality of measurement spots located on the skin area. This is particularly important for curved skin areas, as mentioned above. Without acquiring 3D image information of the skin area, the actual respective spot distances cannot be determined, since only the projected distances are determined.

[0017] According to the principles of the invention, with knowledge of the actual spot distances, a number of first detection signals are assigned to the respective spot distances and to the illumination spots for which the respective spot distances are determined. This is done by a processing unit, which obtains the first detection signals derived from the images recorded by the camera. The processing unit is thus configured to extract information about the locations of the plurality of measurement spots and the illumination spots from said recorded images and to determine the distances between them by any kind of image recognition known in the art, such as statistical techniques, structural techniques, template matching, neural network approaches, fuzzy models and hybrid models.

[0018] In this context, the respective spot distance is the distance between the measurement spot from which the respective first detection signal is derived and the illumination spot (of a plurality of illumination spots, if a spot pattern is used for illumination). This further allows to reduce the noise level by averaging the first detection signals assigned to the same illumination spot and respective spot distances smaller than a threshold distance value, and averaging the PPG signals derived from homogeneous skin areas. This threshold distance value is arbitrary and is set by the processing unit or manually by the user, depending on the location on the subject's skin area where the PPG signal is measured. Typical values ​​range from a few millimeters to a few centimeters.

[0019] By averaging multiple signals, the high noise inherently associated with radial PPG can be reduced by averaging multiple pixels (from multiple measurement spots) with substantially equal distances to the illumination spot in a given area. This is particularly important for radial PPG because even though the relative pulsatile signal (AC / DC) in radial PPG is large, the DC component is very small and therefore very noisy. This is for two reasons. First, the averaging is usually done over fewer pixels compared to wide-field PPG, where a larger skin area is uniformly illuminated, and second, the DC signal is measured farther from the illumination spot and is much weaker since much of the signal strength is absorbed by the skin.

[0020] According to an embodiment, the processing unit is further configured to derive a first detection function from the first detection signals assigned to the same illumination spot, where the first detection function is a function of the spot distance. As mentioned above, using 3D image information of the skin area allows to determine the actual spot distance, not the projected spot distance. Thus, knowledge of the actual distance in the skin area relative to the illumination spot is determined. This allows to derive a first detection function, which is a function of said lateral distance away from the illumination spot. By analyzing the first said detection function and further processing the first detection signals (for example by calculating the respective vital signs or simply by determining the respective relative PPG amplitudes), the spatial resolution of the physiological signal can be obtained. This is used, for example, to define a color map, which represents the PPG amplitudes of the different skin pixels of the measured skin area. Thus, an improved color map is obtained, which can give further support to clinicians and increase the acceptance of PPG imaging in medical environments.

[0021] According to another embodiment, the processing unit is configured to determine 3D information of the skin area from a plurality of first detection signals when the skin area is illuminated with a plurality of illumination spots. Preferably, the light emitted by the illumination unit illuminating the subject is infrared light. Structured infrared light projection is a commonly known technique in depth imaging. If the processing unit is configured by itself to determine 3D information of the skin area from a plurality of first detection signals, no external sensor (such as a time-of-flight (TOF) sensor) is required to obtain 3D depth information. Thus, a compact device is presented that can determine more accurate vital signs by being configured by itself to determine depth information. Thus, the device is a compact and portable device, which can be used not only in stationary clinical environments but also, for example, for ambulatory patients.

[0022] According to another embodiment, the processing unit is configured to determine, for a plurality of illumination spots, a respective spot distance between each measurement spot and an illumination spot that is the closest illumination spot to each measurement spot in relation to the other illumination spots for a plurality of first detection signals. Thus, only the respective distances between the measurement spot and the illumination spots that are close to each other need to be considered to determine the respective distances between them. This reduces the processing time, allowing a quick determination of the respective spot distances and the allocation of all measurement spots to the respective illumination spots.

[0023] According to another embodiment, the processing unit comprises: - obtaining a second detection signal derived from a spatial integral of all electromagnetic radiation reflected from an area of ​​the subject's skin illuminated with one or more illumination spots or derived from electromagnetic radiation reflected or transmitted from an area of ​​the subject's skin illuminated by homogenous illumination; - configured to determine one or more normalization signals, the normalization signals being calculated by calculating a ratio between a first detection signal and a second detection signal of the plurality of first detection signals.

[0024] Preferably, this second detection signal is also derived from the image recorded by the camera. The second detection signal is therefore derived from the spatial integral of the electromagnetic radiation reflected from all illuminated skin pixels. The second detection signal is a wide-field PPG signal. Wide-field PPG is usually measured using a light source that emits electromagnetic radiation uniformly on the subject's skin area. However, it also works well using structured light, i.e. patterns of dots, stripes, circles, etc. In fact, it works with any non-homogeneous illumination pattern, although with a large deconvolution capability. Moreover, using only spot illumination (i.e. one laser spot on the subject's skin) and determining the spatial integral of all the light reflected from the subject's skin is also suitable to provide wide-field PPG.

[0025] The normalized signal is determined by calculating a ratio between a first detection signal of a plurality of first detection signals (radial PPG signals) and a second detection signal (wide-field PPG signal). Preferably, the first detection signal and the second detection signal are derived from electromagnetic radiation of the same wavelength, typically electromagnetic radiation in the near-infrared spectral range. Thus, the normalized signal represents a signal related to electromagnetic radiation in the near-infrared spectral range. In context, the first normalized signal is a measure of the penetration depth of electromagnetic radiation in the near-infrared spectral range in the skin of the subject, since the ratio between the radial PPG signal and the wide-field PPG signal allows obtaining an estimate of the depth of the pulsating layer in the skin area. This is very advantageous compared to conventional PPG imaging, which always has ambiguity problems. More specifically, in conventional PPG imaging, the actual PPG amplitude is difficult to interpret, since it is the integral of the PPG modulation due to different skin depths. A shallow vessel with very little pulsation gives the same PPG signal intensity as a deep vessel with strong pulsation, for example.

[0026] As disclosed herein, by determining the normalized signal, the depth of the pulsatile blood vessels is estimated, which allows for more accurate and less ambiguous interpretation of the PPG images.

[0027] The above system according to the invention comprises an illumination unit configured to emit electromagnetic radiation to illuminate a skin area of ​​a subject with one or more illumination spots. These illumination spots have the shape of a dot, a circle, an ellipse or a stripe. Thus, in the context, the term "spot" is not limited to any kind of shape. It is noted that the circle has some advantages since the number of pixels in the dynamic range of the camera that records the image of the detected electromagnetic radiation reflected from the skin area is increased compared to other illumination profiles such as dots.

[0028] The system further comprises a time-of-flight (TOF) sensor for determining 3D image information of the skin area from detected electromagnetic radiation illuminated with one or more illumination spots and reflected from the skin area, and / or a stereo depth sensor for determining 3D image information by stereo vision. Another option is to assume a 3D skin model (such as a 3D face model), estimate the 3D face pose and use this as 3D image information. Another option is to combine various different sensors, such as TOF and stereo depth sensors, into one combined sensor approach.

[0029] As mentioned above, the processing unit of the device is configured to determine 3D image information of the skin area from the multiple first detection signals when the skin area is illuminated with multiple illumination spots. When the skin area is illuminated with only one illumination spot, there is an option to use a TOF sensor and / or a stereo depth sensor to obtain the 3D image information required to determine more accurate vital signs. The advantage of the stereo depth sensor is that, in contrast to other sensors for depth detection, such as time-of-flight cameras or structured light, stereo vision can be used even in outdoor sunlight, since it is a purely passive process. This allows accurate 3D perception to be provided even under difficult conditions, such as bright sunlight, long distance measurements, or overlapping ranges.

[0030] According to an embodiment, the system further comprises a control unit, preferably connected to the lighting unit and the camera. If the lighting unit is configured to emit electromagnetic radiation with one or more lighting spots having a circular or elliptical shape, said control unit is configured to receive 3D image information of the skin area and a color image of the illuminated skin area recorded by a camera, which is a color camera. The 3D depth information is in an embodiment received from a processing unit of the device, which processing unit is configured to determine the 3D image information by itself or from a TOF sensor and / or from a stereo depth sensor. Based on the received 3D image information and the color image, the control unit can control the shape of the one or more lighting spots emitted by the lighting unit so that the one or more lighting spots emit one or more lighting spots having a shape like an ellipse, having a shape of a circle, on the skin area in the color image recorded by the color camera. This can be done by using any suitable type of image recognition by the control unit to recognize the shape of the ellipse in the received recorded image and adapt the shape of the emitted ellipse based thereon.

[0031] All this is particularly interesting if the skin surface is not perpendicular to the illumination direction, since in this case the circle projected on the skin surface may result in an elliptical shape in the image recorded by the camera. However, according to some embodiments, an elliptical shape is undesirable. An ellipse breaks the circular symmetry, making the post-processing of the acquired signal much more complicated. Therefore, the control unit controls the illumination of the illumination unit so that the image recorded by the camera again contains a circular spot.

[0032] These and other aspects of the invention will be apparent from and elucidated with reference to the embodiments described hereinafter. [Brief description of the drawings]

[0033] [Figure 1A] FIG. 1A is a schematic diagram showing the path of electromagnetic radiation through a subject's skin area for wide-field PPG. [Figure 1B] FIG. 1B is a schematic diagram showing the path of electromagnetic radiation through a subject's skin area for radial PPG. [Figure 2A] FIG. 2A is a schematic diagram showing the detected reflected light of a wide-field PPG. [Figure 2B] FIG. 2B is a schematic diagram showing the detected reflected light of a radial PPG. [Diagram 3] FIG. 3 is a schematic diagram of a Monte Carlo simulation of the path of light through a subject's skin area for radial PPG. [Figure 4A-4B] FIG. 4 is a schematic diagram showing the path of electromagnetic radiation through a subject's skin area in radial PPG. [Figure 5A-5C] FIG. 5 is a schematic diagram illustrating the ambiguity problem that occurs in conventional PPG. [Figure 6] FIG. 6 illustrates a system for determining a subject's vital signs according to the present invention. [Figure 7] FIG. 7 illustrates a modified embodiment of the system shown in FIG. 6 to uniformly illuminate the skin area. [Figure 8]FIG. 8 is a flow chart illustrating a method performed by a device according to the present invention. [Figure 9] FIG. 9 is a schematic diagram illustrating the problems arising from radial PPG without knowledge of the 3D structure of the measured skin area. [Figure 10] FIG. 10 shows an infrared image and a 3D depth image of the mannequin. [Figure 11] FIG. 11 is a flow chart illustrating an optional method performed by a device according to the present invention. [Figure 12A-12B] FIG. 12 is a schematic diagram illustrating the problems that arise from conventional radial PPG without knowledge of the 3D structure of the measured skin area. [Figure 13] FIG. 13 is a schematic diagram showing an area illuminated by a spot pattern. [Figure 14A-14B] FIG. 14 is a schematic diagram showing a further possibility for reducing PPG noise. [Figures 15A-15C] FIG. 15 is a schematic diagram showing the projection of a circular pattern onto an area of ​​skin of a subject. [Figure 16] FIG. 16 is a schematic diagram showing a comparison between illumination of a dot pattern and illumination of a circular pattern. [Figure 17] FIG. 17 is a schematic diagram showing locally measured PPG amplitudes. [Figure 18] FIG. 18 illustrates the processing of radial and wide-field PPG signals to overcome problems arising from conventional PPG. [Figure 19] FIG. 19 is a schematic diagram showing a process for obtaining an improved PPG color map. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0034] 1A and 1B show schematic diagrams illustrating the path of electromagnetic radiation 90 through a subject's skin area 12 for wide-field PPG (left) and radial PPG (right). Wide-field PPG has been a commonly used camera mode for many years, where illumination by electromagnetic radiation 90 is distributed uniformly over the entire skin area 12 and the PPG signal is measured over that same skin area 12. This mode is shown in FIG. 1A. Typically, electromagnetic radiation 90 is emitted by multiple illumination sources 200 and travels through the epidermis 13 of the skin area 12 to deeper skin layers with various venules 14 and arterioles 16 before leaving the skin area 12 and being detected by a detection unit 300, such as a camera. The detected electromagnetic radiation and derived PPG signal is the average of all electromagnetic radiation 90 detected by the camera 300.

[0035] FIG. 1B illustrates the radial PPG mode. The simplest form of non-contact radial PPG is to use only one spot of light injection, as shown in FIG. 1B. This is achieved by using a laser configured to emit electromagnetic radiation 90, for example located in the red or infrared spectral range. Radial PPG is in principle very similar to conventional contact probe PPG measurements. The skin area 12 is illuminated by a spot (circle, stripe, dot, ellipse, etc.) and the PPG signal is measured a few millimeters or centimeters away from that illumination spot 20 on the skin area 12. The spot distance 15 between the illumination spot 20 on the skin area 12 and the measurement spot 30 where the PPG signal is measured is typically shown for one reflected beam in FIG. 1B. The radial PPG signal is therefore a signal that is generally dependent on the spot distance 15. More specifically, electromagnetic radiation reflected from the subject's skin area 12 enters the skin area 12 through the epidermis 13 at an illumination spot 20, is reflected from components of the skin area 12, and is reflected from said skin area 12 by exiting the skin area 12 through the epidermis 13 at a measurement spot 30 located at a spot distance 15 away from the illumination spot 20. In other words, the electromagnetic radiation detected by the detection unit 300 is scattered back from the skin area 12 and collects pulsatile information from different venules 14 and arterioles 16 located in the skin area 12 below the epidermis 13.

[0036] According to some embodiments, it will be shown below that the present invention combines PPG signals obtained from these two measurement modes, namely radial PPG and wide-field PPG.

[0037] Figures 2A and 2B show schematic diagrams showing the detected reflected light for wide-field PPG and radial PPG. The schematic diagrams at the top of Figures 2A and 2B are the same as those already discussed with reference to Figures 1A and 1B above.

[0038] 2A shows (at the bottom) a diagram illustrating the detected reflected light of a wide-field PPG environment. For this purpose, the vertical axis shows the detected reflected light (designated "R") and the horizontal axis shows the measurement time. Curve 253 shows the detected reflected light, including a DC component 255 and an AC component 254. The AC component 254 represents the pulsatile component of light absorption originating from pulsatile arterial blood, and the DC component 255 represents the non-pulsatile component including contributions from non-pulsatile arterial blood, venous blood, and other tissues.

[0039] Fig. 2B shows in the middle row three different diagrams of the detected reflected light of a radial PPG environment. For this purpose, the vertical axis shows the detected reflected light and the horizontal axis shows the measurement time. From the three curves 263, 264, 265 it becomes clear that the larger the spot distance 15 between the illumination spot 20 and the respective measurement spot 30, the smaller the DC component of the detected reflected light (see explanation with reference to Fig. 1B). This is shown diagrammatically by the offset of the curves 263, 264, 265 respectively. The reason for this is that when the light travels a longer path through the skin, more light or electromagnetic radiation 90 is absorbed by the skin area 12.

[0040] These dependencies are also shown in the bottom diagram at the bottom of Fig. 2B, which plots on the vertical axis the AC or DC component of the detected reflected light and on the horizontal axis the spot distance 15. A first curve 273 shows the DC component of the detected reflected light and a second curve 274 shows the AC / DC component (relative PPG amplitude) of the detected reflected light. The trends already discussed become evident: the larger the spot distance 15, the larger the ratio AC / DC (the larger the relative pulsatile component).

[0041] 3 shows a schematic diagram of a Monte Carlo simulation of the path of light through a subject's skin area 12 for radial PPG. The light distribution within the skin area 12 is visualized to show different penetration depths 20, which indicate how deeply the incoming electromagnetic radiation 90 penetrates into the skin area 12 before being scattered back from the venules and arterioles.

[0042] Figures 4A and 4B show further schematic diagrams showing even more clearly the path of electromagnetic radiation 90 through a subject's skin area 12 for radial PPG. As shown in Figure 4A, electromagnetic radiation 90 enters the skin area 12 at an illumination spot 20, is reflected from components of the skin area 12 (mainly venules 14 and arterioles 16), and leaves the skin area 12 at a measurement spot 30 at a distance away from the illumination spot 20. Typically, three different measurement spots are shown in Figure 4A. These three different measurement spots 30 are typically 0.1 mm, 0.2 mm, and 0.3 mm away from the illumination spot 20 where the pencil beam (e.g., laser beam) hits the skin surface.

[0043] In Fig. 4B the light intensity of the detected electromagnetic radiation 90 derived from three different measurement spots 30 as a function of the measurement time is shown. The AC and DC components of the three different curves 413, 414 and 415 clearly depend on the time that the electromagnetic radiation 90 has travelled through the tissue. It becomes clear that the longer the light travels through the skin area 12 with the pulsating volume absorber, the greater the modulation depth of its intensity.

[0044] FIG. 5 shows a schematic diagram illustrating the ambiguity problem that occurs in conventional PPG. While PPG images provide an indication of blood perfusion, as shown in FIG. 4A and FIG. 4B, the actual amplitude (i.e., the ratio of AC and DC components, also called normalized pulsatility) is difficult to interpret because it is the integral of the PPG modulation resulting from reflected light from different skin depths 20. Thus, as shown in the left diagram of FIG. 5, a shallow vessel with very little pulsatility gives the same PPG signal intensity as a deep vessel with strong pulsatility, as shown in the right diagram. Thus, as shown in FIG. 5, different locations of the strongly or weakly pulsating components in the skin area 12 will have exactly the same PPG signal intensity as shown by the curve I(t) in the upper diagram.

[0045] 6 shows a system 500 for determining a vital sign of a subject according to the present invention. The system 500 comprises at least an illumination unit 200, a detection unit 300 and a device 100 for determining a vital sign of a subject. A more detailed description of said device 100 is given below with reference to FIG. 8.

[0046] The illumination unit 200 is configured to emit electromagnetic radiation 90 to illuminate the subject's skin area 12. Preferably, the illumination unit 200 is configured to emit a controllable narrow beam of electromagnetic radiation 90, preferably located in the visible or infrared spectral range. Infrared radiation is preferred in some clinical environments as it is invisible so as not to disturb the patient.

[0047] According to the embodiment shown in Fig. 6, the system 500 optionally further comprises a support 250 for limiting the subject's skin area 12 to a limited skin area to be measured. The support 250 can be placed on the subject's skin as shown in Fig. 6 and is preferably made of a material that is opaque to the incoming electromagnetic radiation 90. Therefore, further preferably, the skin area 12 used for the measurement is limited to an area including a skin area 12 having a homogenous surface along the area to be measured.

[0048] 6 shows a photograph of an illumination profile of an illumination spot 20 on a skin area 12. It is to be understood that the single illumination spot 20 is merely representative. The illumination unit 20 is also configured to project an illumination pattern, i.e., multiple illumination spots, on the skin area 12 of the subject.

[0049] Figure 7 shows a modified embodiment of the system shown in Figure 6 for uniformly illuminating a skin area. To said purpose, the system 500 comprises a diffuser 220 configured to diffuse the controllable narrow beam of electromagnetic radiation 90 emitted by the illumination unit 200 to generate a homogenous illumination profile and / or structured light on the subject's skin area 12. Thus, the configuration shown in Figure 7 allows wide-field PPG to be measured.

[0050] It shall be understood that there is also the option of using separate illumination units to measure wide-field PPG with homogenous illumination and radial PPG with spot illumination. However, the embodiment shown in Fig. 7 provides an advantage since a first measurement for measuring radial PPG can be performed by not placing a diffuser in the path of the emitted electromagnetic radiation 90, and a second measurement for measuring wide-field PPG can be performed by placing a diffuser in the path of the emitted electromagnetic radiation 90. It will be explained below that according to some embodiments of the present invention, the PPG signals acquired for radial PPG and wide-field PPG are combined.

[0051] FIG. 8 shows a flow chart illustrating a method performed by device 100 for determining a subject's vital signs in accordance with the present invention.

[0052] The device 100 comprises a processing unit 110 for obtaining, in step S10, a plurality of first detection signals 120 derived from electromagnetic radiation 90 from a plurality of measurement spots on the subject's skin area 12 illuminated by one or more illumination spots 20, the electromagnetic radiation 90 entering the skin area 12 at the one or more illumination spots 20 and leaving the skin area 12 at a plurality of measurement spots 30. This has already been discussed with reference to Figure 4A, in which one illumination spot 20 is typically shown, through which the electromagnetic radiation 90 enters the skin area 12.

[0053] In step S20, the processing unit 110 obtains 3D image information 130 of the skin area 12. The processing unit obtains the 3D image information from an external sensor or determines the 3D image information of the skin area 12 from a plurality of first detection signals, especially when the skin area 12 is illuminated by a plurality of illumination spots 20.

[0054] In step S30, the processing unit 110 determines for a plurality of first detection signals 120, respective spot distances 15 between respective measurement spots 30 and illumination spots 20 based on the acquired 3D image information 130 of the skin area 12. In step S40, the processing unit 110 assigns the plurality of first detection signals 120 to respective spot distances 15 and illumination spots 20 for which the respective spot distances 15 are determined. Subsequently, the processing unit 110 performs either i) steps S50 and S60, or ii) steps S70 and S80. Thus, in step S50, the processing unit 110 averages the first detection signals 120 assigned to the same illumination spot 20 and respective spot distances 15 smaller than a threshold distance value to obtain an averaged first detection signal 140, and in step S60 determines an averaged vital sign 160 from the averaged first said detection signals. Alternatively, the processing unit 110 determines, in step S70, vital signs 150 from first detection signals 120 assigned to the same illumination spot 20 and respective spot distances 15 smaller than the threshold distance value, and averages, in step S80, said vital signs 150 to obtain an averaged vital sign 160. It is to be understood that these two options are equivalent. Thus, the averaging can be done before or after determining the vital signs.

[0055] FIG. 9 shows a schematic diagram illustrating the problems arising from radial PPG without knowledge of the 3D structure of the skin area. Typically, a module 210 comprising an illumination unit 200 for emitting electromagnetic radiation is used to illuminate a subject's skin area 12 (e.g., head) by a number of illumination spots 20. Furthermore, the module 210 comprises three cameras 300 configured to record images of the detected electromagnetic radiation 90 reflected from the skin area 12 illuminated by the number of illumination spots 20. This is to be understood as merely exemplary. Generally, at least one camera 300 and at least one illumination unit 200 are required, but they also do not have to be integrally formed in one module, as typically shown in FIG. 9.

[0056] The distance between the illumination spots 20 on the subject's forehead (indicated by arrows 914) is easily determined by the distance to the subject to the module 210, i.e. for example by using a Time of Flight TOF. For said purpose, the system as shown in Figures 6 and 7 further comprises for example a TOF sensor configured to determine 3D image information of the skin area 12. Another option is to use for said purpose a stereo depth sensor, whereby distance information is obtained by stereo vision.

[0057] Unlike the spots 20 on the subject's forehead, the problem arises from the distance between the illumination spots 20 on the cheeks (as indicated by the arrows 913 and 915). Said distance is large due to the angle of the skin with respect to the illumination direction. Therefore, without knowledge of the 3D structure of the skin area 12, it is not possible to quantitatively interpret the PPG signal, since only the projection distance is determined from the color image recorded by the camera 300. This leads to the drawback that the radial PPG signal is erroneously assigned to the projection distance instead of the actual distance.

[0058] The present invention overcomes said problem by using 3D depth image information, which allows to determine the actual distance of the illumination spot 20 on the surface of the skin area 20, and not just the projected distance. Another advantage arising from the present invention is that by having knowledge of the 3D structure of the skin area, multiple measurement spots from a homogenous skin area can be averaged to increase the PPG signal strength.

[0059] FIG. 10 shows an infrared image (left) and a 3D depth image (right) of a mannequin. Illuminating an object with a spot pattern in order to extract depth information is a well-known technique. For said purpose, an infrared pattern is projected onto the object (i.e. the mannequin shown in FIG. 10) and one or more standard CMOS sensors of the camera, for example, image the reflected light. Then, using knowledge of the projected light pattern or (if images of at least two CMOS sensors are used) a disparity estimation can be used to estimate the depth of each pixel. This is achieved, for example, by using the module 210 shown in FIG. 9, where an infrared pattern is projected onto the subject and used to infer the depth using three cameras.

[0060] FIG. 11 shows a flow chart illustrating an optional method executed by the processor 110 of the claimed device 100. As already explained with reference to FIG. 8, in step S10, the processor obtains first detection signals derived from electromagnetic radiation 90 from a plurality of measurement spots on the skin area 20 of the subject. When the skin area 12 is illuminated by a plurality of illumination spots 20, the processor determines 3D image information from a plurality of first detection signals 120 in step S22. Thus, the processor determines this information independently without obtaining this 3D information from an external sensor (such as a TOF sensor). This provides the advantage that no external sensor configured to measure depth information is required. Thus, the device 100 with the processor 110 is a compact device, which is further portable for use in a variety of different environments, such as non-stationary environments and ambulatory patients.

[0061] Figures 12A and 12B show schematic diagrams illustrating the problems arising from conventional radial PPG without knowledge of the 3D structure of the measured skin area 12, as in Figure 9. As already mentioned above, radial PPG aims to measure light intensity as a function of lateral (radial) distance away from an illumination spot 20. Typically, one illumination unit 200 is shown illuminating the skin area 12 by one illumination spot 20. A camera 300 detects the electromagnetic radiation reflected from the skin area 12, and only the reflected light within the field of view FOV of the camera 300 is detected.

[0062] 12A shows a scenario in which the surface of the skin area 12 is perpendicular to the illumination direction of the illumination unit 200. In other words, the normal of the plane defined by the skin surface is parallel to the illumination direction. In this case, the distance in the skin area is easily determined by the distance from the skin area 12 to the camera 300, i.e., by measuring said distance, for example, using a TOF technique. Typically, the unit distance and the distance r are shown, while the distance r is the spot distance 15 between the illumination spot 20 and the measurement spot 30 (as explained above).

[0063] Fig. 12B shows a scenario where the surface of the skin area is not perpendicular to the illumination direction of the lighting unit 200. In this case, without knowledge of the 3D structure of the skin area 12, the distance in the skin area 12 cannot be easily determined. This is again indicated by the same unit distance and distance r. The length of the arrow indicating said unit distance and distance r (i.e., spot distance 15) is shorter than that of the arrow in Fig. 12A. This indicates that the projection needs to be corrected when the skin is not perpendicular to the illumination direction of the lighting unit 200. Otherwise, the measured radial PPG signal will be assigned to the projected (small) distance instead of the actual (correct) distance.

[0064] Figure 13 shows a schematic diagram showing the area illuminated by the spot pattern, which is the skin area illuminated for PPG measurements, as described above.

[0065] The same module 210 as already described with reference to Fig. 9 is used here, comprising an illumination unit 200 and three cameras 300. The illumination unit 200 illuminates the skin area 12 by means of a number of illumination spots 20. Typically, the illumination spots 20 have the shape of a dot. However, it shall be understood that the illumination spots 20 can also have the shape of a line, an ellipse, a circle, etc.

[0066] Each dashed circle around the illumination spot 20 represents a possible measurement spot 30, all of which have the same spot distance 15 to the respective illumination spot 20. Thus, the measurement spots in the inner dashed circle typically have a spot distance of 1 mm to the respective illumination spot 20. The measurement spots in the outer dashed circle typically have a spot distance of 2 mm to the respective illumination spot. Thus, the first detection signals derived from electromagnetic radiation from multiple measurement spots on a skin area of ​​a subject illuminated with multiple illumination spots are abbreviated as I(r=1 mm) and I(r=2 mm), respectively, as shown in FIG. 13. If the area is not flat but curved, i.e., the area is not perpendicular to the illumination direction of the illumination unit 200, the dashed circle is transformed into a dashed ellipse, which represents the problem already discussed with reference to FIG. 9 and FIG. 12. Thus, the dashed circle is transformed into an ellipse for a curved area, as shown at the bottom of the area shown in FIG. 13.

[0067] 14A and 14B show schematic diagrams illustrating the use of multiple modules 210, each with a lighting unit 200 and three cameras 300. A powerful technique is to reduce the noise of the measured first detection signal by combining multiple modules 210 and registering these camera images using spot patterns. As shown in FIG. 14A, one of the modules 210 is used to project the lighting pattern (as indicated by the arrow) and the other modules are used only for imaging, i.e., to record the electromagnetic radiation reflected from an area (such as the measured skin area). FIG. 14B shows a schematic diagram illustrating the use of ten modules as a module array 211. The vertical arrangement allows placing ten (or more) modules 210 at a small distance with limited parallax. Thus, the noise is further reduced by averaging the signals obtained from the multiple modules 210.

[0068] Fig. 15 shows a schematic diagram illustrating the projection of a pattern of circles onto a skin area of ​​a subject. The skin area 12 is either on the subject's head as shown in Fig. 12A or on the hand as shown in Fig. 12B. However, it should be understood that these two skin areas are merely exemplary. It should be noted that while measuring the PPG signal from the subject's cheek or forehead as shown in Fig. 15A is well known to give adequate PPG signal strength, measuring the PPG signal at other anatomical locations, such as the arm, is known to give much lower PPG signal strength.

[0069] As shown in Fig. 15A, the lighting unit 200 is used to project a circular pattern onto a subject's skin area 12 located at a distance D from the lighting unit 200. An image of such a pattern projected onto the subject's hand is shown in Fig. 15B. This image is recorded by a camera 300, shown in Fig. 15A, positioned directly adjacent to the lighting unit 200. To correct for parallax, a second camera is used.

[0070] It becomes clear that the shape of the projected pattern depends on the angle α of the skin area 12 with respect to the illumination direction. If this angle is zero, i.e. if the skin area 12 is perpendicular to the illumination direction, the pattern projected on the skin area 12 comprises a circle, whereas if the angle is different from zero, i.e. if the skin area 12 is not perpendicular to the illumination direction, the projected pattern comprises an ellipse. In other words, the projected pattern of a circle appears as an ellipse on the skin area 12 for a non-zero angle α.

[0071] FIG. 15C shows a schematic diagram illustrating the shape of a circle projected at different locations on the skin area 12, indicated by "A" and "B" in FIG. 15A, with location "B" being located further away from the subject's nose than location "A". The angle α is much larger at location "B", while said angle is nearly zero at location "A". Thus, the diameter d of the circle projected at location "A" is Ais significantly modified as shown in FIG. 15C. The projected circle has a modified diameter d A '=d A / cos(α). The diameter d of the circle projected onto the location "B" B is rarely modified (d B ≒d B '). Thus, a circle projected at location "B" appears as a circle and is not converted to an ellipse. This can also be seen in FIG. 15B, where a circle projected at a location where the angle α is large, such as the inside of a finger, appears as an ellipse. It shall be understood that the correction of the projected circle to an ellipse depends not only on the diameter of the projected circle and the angle α, but also on the distance D between the lighting unit 200 and the similar area 12 of the subject.

[0072] It will be shown later that as the spot distance increases (i.e. the distance between the illumination of the spot pattern and the respective measurement spot increases), the PPG signal strength drops significantly. Even with low noise / high sensitivity cameras, this is a very challenging dynamic range. By using a circular illumination pattern, many more camera pixels are within a given dynamic range without losing the ability to measure the radial PPG signal.

[0073] Therefore, the use of only circular patterns has various possibilities. One option is to discard all illumination spots with strong ellipsoidal illumination (e.g., for angles α>10°) for further processing of the PPG signal. Thus, there is an option to discard signals derived from image regions in the recorded image of the camera 200 that contain a lot of ellipsoidal illumination (such as location "A" in FIG. 15A).

[0074] Another option is to modify the illumination of the illumination spot at location "A" so that the actual illumination becomes a circle again. This is done as follows: As shown in Fig. 15A, a control unit 400 is connected to the illumination 200 and the camera 300. Said control unit 400 receives the 3D image information of the skin area 12 and a color image of the illuminated skin area 12 recorded by the camera 300, which is a color camera. Based on this, the control unit 400 controls the shape of the illumination spot emitted by the illumination unit 200 (circular pattern) so that the illumination spot emits an illumination spot having an elliptical shape such that the illumination spot appears again (in the image recorded by the camera 300) as a circular spot.

[0075] FIG. 16 shows schematic diagrams comparing illumination with a dot pattern and illumination with a circular pattern. The top three figures show the DC component of the reflected intensity depending on the spot distance 15 respectively. In the case of the circular spot pattern, the spot distance is again determined by the (minimum) distance of the respective measurement 30 spot to the illumination spot 20. The upper curve in each figure shows the reflected intensity derived for a circular spot pattern, and the lower curve for a dot pattern. The left figure shows the reflected intensity derived for a circular spot pattern with a projected spot diameter of 1 mm. The middle and right figures refer to illumination with a circular diameter of 3 mm and 5 mm, respectively (see the sketches of the respective circles below). In all three figures, the circular spot pattern curve contains more intensity values ​​than the dot pattern curve, so the drop in DC intensity within the illumination circle is much smaller than in the dot case. This shows that by using a circular illumination pattern, many more camera pixels are within a certain dynamic range without losing the ability to measure the radial PPG signal.

[0076] FIG. 17 shows a schematic diagram of locally measured PPG amplitudes. The color map image on the right displays the amplitude of locally measured PPG amplitudes, while the diagram on the left shows the time signal of the respective PPG amplitudes measured at four different locations in the skin area 12 indicated by the numbers. The color image is difficult to interpret for clinical applications, since the displayed signal is a convolution of PPG modulations due to different skin depths, as already explained with reference to FIG. 5. A superficial vessel with very little pulsatility gives the same PPG signal intensity as, for example, a deeper vessel with stronger pulsatility. Therefore, it is not clear from the color map shown in FIG. 17 whether the large signal in the face area indicated by the number "1" is due to a relatively shallow arteriole or a dense artery, since the overall signal is a weighted sum of the pulsatile components at various depths. This ambiguity is also one of the reasons why PPG imaging has been slow to be accepted in clinical practice. When a clinician interprets a color map, it can be difficult to explain what it actually refers to, since many parameters are involved, such as the optical depth of the pulsating vessels at the wavelength used, the strength of the volume pulsation, the density of the pulsating vessels, the absorption coefficient of blood, etc. With reference to the following Fig. 18, a method is explained that defines the signal used to indicate the optical depth of the pulsating vessels and thus to provide less ambiguous PPG imaging.

[0077] Fig. 18 shows the processing of radial PPG signals and wide-field PPG signals to overcome problems arising from conventional PPG. As explained above, the first detection signal refers to the radial PPG signal, and the processing unit of the claimed device is configured to derive a first detection function 170 from the first detection signals assigned to the same illumination spot 20. The first detection function 170 is a function of spot distance as shown in Fig. 18 and describes the relative pulsating component (AC / DC) of the first detection signal.

[0078] As explained above, the second detection signal refers to a wide-field PPG signal. The processing unit of the claimed device is further configured to derive a second detection function 174 from the second detection signal. Since the second detection function refers to a wide-field PPG and homogeneous illumination, the second detection signal also describes the relative pulsating component (AC / DC) of the second detection signal, but is independent of the spot distance.

[0079] In a next step, the processing unit is configured to determine a normalized signal 190 by calculating the ratio between a first detection function 170 derived from the first detection signal and a second detection function 174 derived from the second detection signal. This normalized signal 190, which refers to the ratio between the radial PPG signal amplitude and the wide-field PPG signal amplitude, can be used to provide an index that depends on the spot distance 15. This index is called the "Optical Depth Index" or "ODI" and represents an estimate of the relative optical depth of the PPG source. In other words, said normalized signal 190 or said ODI provides an estimate of the dominant depth of the pulsating blood vessels. This ODI therefore makes it possible to obtain information about the dominant depth of the pulsating blood vessels to which the electromagnetic radiation is scattered back.

[0080] FIG. 19 shows a schematic diagram illustrating the process of obtaining an improved PPG color map. The top color map represents a typical color map derived from conventional PPG imaging, with the colors representing the intensity of the PPG amplitude. The color map is difficult to interpret, since, as already mentioned above, the overall signal is a weighted sum of pulsatile components at different depths, and it is not clear from the color map whether the large signal in the face region indicated by the number "1" is due to relatively shallow arterioles or whether there is a higher density of arteries. However, as explained with reference to FIG. 18, the ratio of the radial PPG signal to the wide-field PPG signal gives an index ODI that allows to estimate the penetration depth of the electromagnetic radiation in the subject's skin. This ODI depends on the spot distance 15, as shown in the right diagram of FIG. 18. Therefore, for simplicity, a constant ODI value is defined, for example, by setting the spot distance to 1 cm. This allows to determine a color map for each skin pixel with a discrete ODI value. This color map is shown in the bottom left of FIG. 19. The color map shows that the ODI in the forehead is usually low, while the ODI in the cheek is usually high. The color map in the lower right of Fig. 19 is the sum of the ODI color map and a color map obtained from conventional PPG imaging, which does not have information about the optical depth of the pulsating layer. Therefore, it is speculated that this color map gives more accurate results and improves PPG imaging, since the PPG signal intensity is weighted by the ODI.

[0081] While the invention has been illustrated and described in detail in the drawings and foregoing description, such illustration and description are to be considered as illustrative or exemplary and not restrictive, and the invention is not limited to the disclosed embodiments. Other variations to the disclosed embodiments can be understood and effected by those skilled in the art in practicing the claimed invention, from a study of the drawings, the disclosure, and the appended claims.

[0082] In the claims, the term "comprising" does not exclude other elements or steps, and the singular does not exclude a plurality. A single element or other unit fulfills the functions of several items recited in the claims. The mere fact that certain measures are recited in mutually different dependent claims does not indicate that a combination of these measures cannot be used to advantage.

[0083] The computer program may be stored / distributed in a suitable non-transitory medium, such as an optical storage medium or a solid-state medium, provided together with or as part of other hardware, but may also be distributed in other forms, such as via the Internet or other wired or wireless communication systems.

[0084] Any reference signs in the claims shall not be construed as limiting the scope.

Claims

1. 1. A device for determining vital signs of a subject, comprising: obtaining a plurality of first detection signals from a plurality of measurement spots on a skin area of ​​the subject illuminated with one or more illumination spots, wherein the plurality of first detection signals are derived from electromagnetic radiation entering the skin area at the one or more illumination spots and exiting the skin area at the plurality of measurement spots; obtaining 3D image information of the skin area; determining a respective spot distance between each of the measurement spots and an illumination spot based on the acquired 3D image information of the skin area for the first detection signals; assigning the plurality of first detection signals to respective spot distances and to the illumination spots for which the respective spot distances are determined; a processing unit for averaging the first detection signals assigned to the same illumination spot and respective spot distances less than a threshold distance value to obtain an averaged first detection signal and determining an averaged vital sign from the averaged first detection signal, or for determining a vital sign from the first detection signals assigned to the same illumination spot and respective spot distances less than a threshold distance value and averaging the vital signs to obtain an averaged vital sign.

2. The device of claim 1 , wherein the processing unit is further configured to derive a first detection function from the first detection signals assigned to the same illumination spot, the first detection function being a function of the spot distance.

3. The device according to claim 1 or 2, wherein the processing unit is adapted to determine the 3D image information of the skin area from the plurality of first detection signals when the skin area is illuminated with a plurality of illumination spots.

4. 4. The device of claim 1, wherein the processing unit determines, for the plurality of first detection signals, a respective spot distance between a respective one of the measurement spots and an illumination spot that is a closest illumination spot to the respective one of the measurement spots in relation to other illumination spots, in the case of a plurality of illumination spots.

5. The processing unit includes: obtaining a second detection signal derived from a spatial integral of all electromagnetic radiation reflected from the subject's skin area illuminated with one or more illumination spots or derived from electromagnetic radiation reflected or transmitted from the subject's skin area illuminated by homogenous illumination; 5. The device of claim 1, further comprising: determining one or more normalized signals, the normalized signals being calculated by calculating a ratio between a first detection signal of one of the plurality of first detection signals and the second detection signal.

6. The device of claim 1 , wherein the plurality of first and second detected signals are derived from electromagnetic radiation of the same wavelength.

7. 1. A system for determining vital signs of a subject, the system comprising: an illumination unit for emitting electromagnetic radiation to illuminate the subject's skin area with one or more illumination spots; a camera configured to record an image of the detected electromagnetic radiation illuminated with one or more illumination spots and reflected from the skin area, and to derive a plurality of first detection signals from the recorded images; and a device according to any one of claims 1 to 6 for determining averaged vital signs of a subject.

8. The system of claim 7 , wherein the one or more illumination spots have any one of the following shapes: a circle, an ellipse, a dot, or a stripe.

9. The system according to claim 7 or 8, further comprising a time-of-flight sensor for determining 3D image information of the skin area from the detected electromagnetic radiation illuminated with one or more illumination spots and reflected from the skin area, and / or a stereo depth sensor for determining 3D image information of the skin area by stereo vision.

10. Further comprising a control unit, 10. The system of claim 7, wherein if the lighting unit emits electromagnetic radiation with one or more lighting spots having a shape of a circle or an ellipse, the control unit receives 3D image information of the skin area and a color image of the illuminated skin area recorded by the camera, which is a color camera, and controls the shape of the one or more lighting spots emitted by the lighting unit based on the received 3D image information and the received color image to emit one or more lighting spots having a shape of an ellipse, such that the one or more lighting spots have a shape of a circle on the skin area in the color image recorded by the color camera.

11. The system according to claim 9 or 10, wherein the processing unit receives the 3D image information from the processing unit of the device, or from a time-of-flight sensor, or from a stereo depth sensor.

12. 12. The system according to claim 7, wherein the camera comprises a plurality of detection elements, in particular an array of photodiodes, a CCD array or a CMOS array.

13. 1. A computer-implemented method for determining vital signs of a subject, the method comprising: obtaining a plurality of first detection signals from a plurality of measurement spots on a skin area of ​​the subject illuminated with one or more illumination spots, the plurality of first detection signals being derived from electromagnetic radiation entering the skin area at the one or more illumination spots and exiting the skin area at the plurality of measurement spots; obtaining 3D image information of the skin area; determining a respective spot distance between each of the measurement spots and an illumination spot based on the acquired 3D image information of the skin area for the plurality of first detection signals; assigning the plurality of first detection signals to respective spot distances and to the illumination spots for which the respective spot distances are determined; and averaging the first detection signals assigned to the same illumination spot and respective spot distances less than a threshold distance value to obtain an averaged first detection signal and determining an averaged vital sign from the averaged first detection signal, or determining a vital sign from the first detection signals assigned to the same illumination spot and respective spot distances less than a threshold distance value and averaging the vital signs to obtain an averaged vital sign.

14. A computer program comprising program code means for causing a computer to carry out the steps of the method according to claim 13 when said computer program is executed on said computer.

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