Device and method for analyzing a material

Abstract

The invention relates to an apparatus for analyzing a material comprising an excitation emission device for generating at least one electromagnetic excitation beam, in particular an exciting light beam, having at least one excitation wavelength, further comprising a detection device for detecting a reaction signal, and a device for analyzing the material on the basis of the detected reaction signal.

Claims

1. A method for analysing a material comprising: applying the material to an optical medium such that a first surface region of the material is in direct contact with the optical medium at an interface; radiating at least one electromagnetic excitation beam having at least one excitation wavelength into a radiation volume of the material located underneath said interface; modulating the intensity of the at least one electromagnetic excitation beam with one or more modulation frequencies; delivering a measuring beam through the optical medium to reflect at the interface and create a reflected measuring beam, wherein the measuring beam and the at least one electromagnetic excitation beam are directly adjacent or overlapping on said interface, and wherein said optical medium is transparent to the measuring beam; detecting a time-dependent response signal from said reflected measuring beam by at least one of receiving said reflected measuring beam and detecting a deflection of the reflected measuring beam, wherein the time-dependent response signal is detected as a function of: (i) the at least one excitation wavelength, (ii) the intensity modulation of the at least one electromagnetic excitation beam, and (iii) a response signal phase position in relation to a modulation phase of the at least one electromagnetic excitation beam; determining an intensity distribution of the time-dependent response signal as a function of depth beneath the interface within the radiation volume in which the response signals are generated, based on the response signal phase position in relation to the modulated excitation beam at one or more modulation frequencies of said excitation beam; and analysing the material based on the time-dependent response signal and the intensity distribution.

2. The method according to claim 1, wherein the at least one electromagnetic excitation is directly coupled to the optical medium.

3. The method according to claim 1, wherein modulating the intensity of the at least one electromagnetic excitation beam comprises at least one of electrically controlling the at least one electromagnetic excitation beam, controlling a mirror arranged in a beam path of the at least one electromagnetic excitation beam, and controlling transparency of a layer arranged in the beam path.

4. The method according to claim 1, wherein at least one of the beams is delivered to the optical medium by either a direct mechanically fixed connection or by a fibre-optic cable.

5. The method according to claim 1, at least at least one of the beams is delivered to the optical medium by an imaging optics arrangement.

6. The method according to claim 1, wherein the optical medium is characterized by a medium surface with a plurality of partial faces inclined towards each other at which the measuring beam is reflected multiple times.

7. The method according to claim 1, wherein detecting the time-dependent response signal further includes detecting a temporal waveform of the time-dependent response signal and subjecting the temporal waveform to a Fourier transformation.

8. The method according to claim 1, wherein the radiating the at least one electromagnetic excitation beam includes varying an incidence angle of the at least one electromagnetic excitation beam, and wherein analysing the material includes subtracting from each other response signals from different incidence angles to eliminate effects of the upper layers of skin.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

(1) FIGS. 1 to 24 schematically show different elements of the device and its elements, in some cases in different embodiments.

DETAILED DESCRIPTION

(2) FIG. 1 shows an exemplary embodiment of a device 10 for analysing a material 101. The material 101 is preferably placed directly on an optical medium 108, which can be designed as an optically transparent crystal or glass body. The device for analysing the material 101 is used for example to measure the glucose or blood sugar content in a fluid, such as in one embodiment blood, and for producing a glucose or blood sugar level indication BZA.

(3) FIG. 1 shows an exemplary embodiment of a device 10 for analysing a material 101. The material 101 is preferably placed directly on an optical medium 108, which can be designed as an optically transparent crystal or glass body or plastic body or plastic crystal. The device for analysing the material 101 is used for example to measure the glucose or blood sugar content in a fluid, such as in one embodiment blood, and for producing a glucose or blood sugar level indication BZA.

(4) The device comprises an excitation transmission device 100 for emitting one or more electromagnetic excitation beams SA, preferably in the form of excitation light beams with one or more excitation wavelengths, into a volume 103 which is located in the material 101 below a first region 102 of the surface of the material. The excitation transmission device 100 is also referred to in the following as excitation light source 100 for brevity. The excitation light source 100 can be a laser which is tunable with respect to its wavelength, in particular a tunable quantum cascade lasers; it is preferable, as will be explained below, to use a light source strip or a light source array with at least two single emitters, in particular semiconductor lasers, each of which emits a specified individual wavelength.

(5) In addition, a device 104 for the intensity modulation of the excitation light beam or beams SA is provided, which is preferably formed by a modulation device for the excitation light source, in particular for controlling it, and/or by at least one controlled mirror arranged in the beam path and/or by a layer, which is arranged in the beam path and is controllable with respect to its transparency.

(6) In addition, the device has a system 105 for emitting an electromagnetic measuring beam 112, in particular a measuring light beam, which is reflected, preferably totally reflected, at the interface GF between the material 101 and the optical medium 108.

(7) A detection device 106 is used for the detection of the reflected measuring beam 112, which forms a time-dependent response signal SR; the amplitude of the response signal SR is influenced by the wavelength of the excitation light SA and the intensity modulation of the excitation light SA, as will be explained in more detail below by means of examples.

(8) The amplitude of the measuring signal depends on the wavelength of the excitation beam, the absorption properties of the sample and the thermal properties, in particular the thermal diffusivity and thermal conductivity of the sample and of the optical element. In addition, the coupling of the thermal signal from the sample into the optical element also plays a role.

(9) A device 107 for analysing the material evaluates the detected response signals SR and in one embodiment generates a glucose or blood sugar level indication BZA.

(10) Hereafter, the operation of the device 10 in accordance with FIG. 1 and in this connection, an example of a method for analysing a material 101 will be described in more detail for the case in which the material 101 to be analysed is human or animal tissue, and as part of the analysis of the material a glucose or blood sugar level indication BZA is to be determined.

(11) With the device 105 an electromagnetic measurement beam 112, which is preferably a light beam in the visible wavelength range or an infrared light beam, is irradiated into the optical medium 108; this measurement beam 112 impinges on the interface GF below the first region 102 of the surface of the tissue. At the interface GF the measuring beam 112 is reflected and reaches the detection device 106, which measures the reflected measurement beam 112.

(12) At the same time, one or more excitation beams SA, which are preferably infrared beams, are generated with the excitation light source 100. The wavelength of the infrared beams is preferably in a range between 3 ?m and 20 ?m, particularly preferably in a range between 8 ?m and 11 ?m.

(13) The excitation beams SA are intensity- or amplitude-modulated with the device 104 for intensity modulation. In one embodiment short light pulses are generated with the device 104 for intensity modulation, preferably with a pulse frequency of between 1 kHz and 10 MHz, more preferably between 1 kHz and 3 MHz, or else pulse packets (double or multiple modulation), preferably with envelope frequencies of 1 Hz-10 kHz.

(14) The modulated excitation beams SA are coupled into the optical medium 108 and after passing through the interface GF arrive in the volume 103 within the tissue.

(15) The wavelength of the excitation beams SAwith a view to the example of blood glucose measurement explained hereis preferably chosen such that the excitation beams SA are significantly absorbed by glucose or blood sugar. For measuring glucose or blood sugar the following infrared wavelengths are particularly well suited (vacuum wavelengths): 8.1 ?m, 8.3 ?m, 8.5 ?m, 8.8 ?m, 9.2 ?m, 9.4 ?m and 9.7 ?m. In addition, glucose-tolerant wavelengths can be used, which are not absorbed by glucose, in order to identify other substances present and allow for excluding their effect on the measurement.

(16) Due to the absorption of the excitation beams SA in the tissue in the region of the volume 103, a local temperature increase is induced, which triggers a heat transfer and thermal waves and thereby also pressure waves in the direction of the interface GF; due to the resulting temperature and pressure fluctuations at the interface GF, the refractive index and/or the deformation, microstructure and the reflection behaviour are modulated in the region 102 and/or in the reflection region of the interface GF, and the beam path of the measuring beams 112 is affected.

(17) If it is assumed, for example, that without excitation beams SA the alignment between the system 105 and the detection device 106 is optimal and a maximum received power is detected by the detection device 106, then due to the absorption of the excitation beams SA in the region of the volume 103 and due to the heat transport and the pressure waves, an (at least temporary) change in the amplitude or, in the case of a periodic modulation, the phase of the reflected measuring beam 112 can be induced, or an intensity modulation of the reflected measurement beam 112 can occur. The extent of the intensity modulation depends on the wavelength of the excitation beams SA (because of the necessary absorption in the tissue) and on the pulse frequency of the excitation beams SA (due to the temperature transport and the pressure waves from the tissue interior in the direction of the interface GF) and on the thermal properties of the sample and the medium.

(18) The change in the reflection of the measuring beam 112 and/or the time-dependent change in the response signal SR is quantitatively acquired by the detection device 106, and the detection result D reaches the device 107.

(19) On the basis of previously carried out calibration or comparison measurements, which in one embodiment are stored in a memory 107a of the device 107 in the form of comparison tables or comparison curves, the current concentration of glucose or blood sugar within the tissue or within the volume 103 can be deduced and a corresponding glucose or blood sugar indication BZA can be produced. The comparison tables or comparison curves may have been created, for example on the basis of glucose or blood sugar levels which were determined based on blood samples.

(20) Particularly preferred embodiments and variants of devices 10 for analysing a material 101 are described below with reference to FIGS. 2 to 10.

(21) The excitation transmission device 100 for emitting the excitation light beam or beams can be designed as an array, as shown in FIG. 2. The array has at least 5, advantageously at least 10, more advantageously at least 15 or at least 50 or 100 individually controllable emitters 100a for monochromatic light in the absorption spectrum of a material to be analysed.

(22) The array preferably generates beams with monochromatic light with one or more, particularly preferably all of the following wavelengths (vacuum wavelengths): 8.1 ?m, 8.3 ?m, 8.5 ?m, 8.8 ?m, 9.2 ?m, 9.4 ?m and 9.7 ?m and if desired, in addition glucose-tolerant wavelengths.

(23) The device 105 for emission of the measuring light beam 112 and the detection device 106 can be arranged separately from the optical medium 108, as shown in FIG. 1. With a view to a minimal space requirement and minimal installation effort, it is regarded as advantageous if the device 105 for the emission of the measuring light beam 112 and the detection device 106 108 are mounted directly on the optical medium, preferably on opposite surface sections 108a and 108b of the optical medium 108, as FIG. 3 shows.

(24) It can be provided that the excitation device/excitation light source 100 is permanently mechanically connected to the optical medium 108 either directly or by means of an adjustment device 109. The adjustment device 109 preferably allows an adjustment of the distance of the excitation light source 100 from the optical medium 108, and/or an adjustment in the beam longitudinal direction and/or an adjustment in a plane perpendicular thereto (see FIG. 4).

(25) As shown in FIGS. 3, 4, 6, 7 and 8, the device 105 can be provided for emission of the measuring light beam 112 into the region of the optical medium 108 that is in contact with the first region 102 of the material surface. Such an arrangement allows the measuring light beam 112 to be irradiated at a flat angle and a total internal reflection to be induced at the interface of the optical medium 108 with the material 101.

(26) By injecting the radiation at a flat (small) angle (to the sample surface), the mirage deflection, analogously to the known photothermal Bouncing Method, can be made more effective and at the same time the deformation-induced deflection of the measuring beam can be reduced. The angle between the sample surface and the measuring beam in one embodiment can be selected to be less than 20 degrees, less than 10 degrees, in particular less than 5 degrees, more particularly less than 2 degrees or 1 degree, in order to exploit this effect.

(27) Conversely, by providing the irradiation at steeper (larger) angles (to the material surface), by analogy to the known photothermal Bouncing Method the deflection can be made more effective and at the same time the mirage-effect related deflection of the measuring beam can be reduced. The angle between the material surface and the measuring beam in one embodiment can be selected to be greater than 20 degrees, greater than 30 degrees, in particular greater than 45 degrees, more particularly greater than 60 degrees or 70 degrees, to exploit this effect.

(28) See related literature: M. Bertolotti, G. L. Liakhou, R. Li Voti, S. Paolino, and C. Sibilia. Analysis of the photothermal deflection technique in the surface refection theme: Theory and Experiment. Journal of Applied Physics 83, 966 (1998)

(29) The device 105 for emitting the measuring light beam 112 and/or the detection device 106 for detecting the measuring light beam 112 and/or the response signal SR, can be mechanically connected to the optical medium 108 in a supportive manner either directly or by means of an adjustment device, and/or coupled thereto by means of one or more fibre-optic cables 120.

(30) It can also be provided, as shown in FIG. 6, that the optical medium 108 directly supports an imaging optics 128 and/or an imaging optics 129 (in each case) in the form of a lens or other reflection or refraction means, and/or that an imaging optics is integrated into the optical medium 108. The imaging optics can, however also be integrated into the excitation transmission device or the device for generating the measuring beam, for example, in the form of a lens or other reflection or diffraction element, if these are designed as integrated components and/or as a semiconductor component. The imaging optics can in one embodiment be subtractively formed from the same semiconductor element by etching as the respective integrated circuit, which has a radiation source for the excitation or measuring beam.

(31) It can also be provided, as shown in FIG. 7, that the surface of the optical medium 108 has a plurality of partial faces 110, 111 inclined towards each other, at which the measuring light beam 112, is reflected or refracted multiple times.

(32) It can also be provided, as shown in FIG. 3, that in or on the optical medium 108 one or more mirror surfaces 113, 114 are provided for reflecting the measuring light beam 112 (and therefore the response signal SR.) These mirror surfaces can be formed by inhomogeneities within the optical medium 108 or by its outer surfaces or by means of, for example, metallic or metallic coated mirror elements that are integrated/fitted/cast-in or mounted on the optical medium. This extends the optical path of the measuring light beam 112 in the optical medium 108 until its entry into the detection device 106, so that in the case of reflection at the region of the surface of the medium 108, which is in contact with the first region 102 of the material surface, a response signal-dependent deflection of the measuring light beam 112 within the optical medium 108 is increased. The deflection can then be detected in the detection device 106 as an absolute deflection.

(33) The detection device 106 can have a plurality of optically sensitive surfaces, such as optically sensitive semiconductor diodes, or else a plurality of staggered openings 116, 117, 118 in a connector body 119 (FIG. 5), at which individual fibre-optic cables 120 end (FIG. 4), into which the light of the measuring light beam 112 is coupled depending on its deflection. The fibre-optic cables 120 are then connected to a connector body 119, which can be fixed to the optical medium 108, and direct the light to the part of the detection device 106 arranged at the end of the fibre-optic cable 120 (FIG. 4). The connector body 119 is then, in the same way as the fibre-optic cable 120, also part of the detection device 106 for detecting the measuring light beam.

(34) For the sake of completeness, it should be noted that the excitation transmission device can also send the excitation to the material surface either as a whole or section by section by means of one or more fibre-optic cables, and in one embodiment the excitation transmission device can be directly coupled to one or more fibre-optic cables, which are coupled to the optical medium.

(35) It can also be provided, as shown in FIG. 8, that the excitation transmission device 100, the device 105 for emitting the measuring light beam 112, and the detection device 106 are directly attached to each other or to a common support 121. The support can be formed by a plastic part, a printed circuit board or a metal sheet, which is mounted in a housing 122. The support, which in FIG. 8 is formed with a U-shaped cross section, can then at least partially surround the optical medium 108 in one embodiment. The optical medium can be attached to the support and adjusted relative to it.

(36) The support can also be formed by the housing 122 itself or a housing part.

(37) It can also be provided that the device with the housing 122 can be fastened to the body 123 of a person, wherein the excitation transmission device 100 for emitting one or more excitation light beams SA, the device 105 for emitting the measuring light beam 112 and the detection device 106 for detecting the time-dependent response signal SR are arranged and configured in such a way that the side that is suitable for performing the measurement (with a measuring window transparent to the excitation radiation) of the device is located on the side of the device facing away from the body, so that the material to be analysed can be measured on the side 124 of the housing 122 facing away from the body 123. In relation to this, FIG. 8 shows that the housing 122 is attached to the body 123 of a person by means of a belt 125 belonging to the housing 123, in one embodiment being in the form of a bracelet on a wrist. On the opposite side 124 from the wrist, the housing then has a window which is transparent to the excitation light beam SA, or the optical medium 108 is fitted directly into the outwards facing side 124 of the housing and itself forms the surface of some sections of the housing.

(38) As shown in FIG. 8, a fingertip 126 shown schematically by a dashed line can then be placed on the optical medium 108 and measured.

(39) The optical medium 108 can be attached within the housing 122, in the same way as the support 121, or else directly attached to the housing 122. The optical medium 108 can also be directly connected to the support 121, wherein an adjustment device 127 should be provided for the relative positioning of the support 121 with respect to the optical medium.

(40) It is also conceivable to attach the excitation light source 100, the device 105 and the detection device 106, or even just one or two of these elements, directly to the optical medium 108 and the other element or elements to the support 121.

(41) Through the optical window in the housing 122 and/or through the optical medium 108, other parameters of the material surface or the positioned fingertip 126 can be measured, such as in one embodiment, a fingerprint. For this purpose, in the housing an optical detector 130 in the form of a camera, for example, can be fastened to the support 121, which records a digital image of the material surface through the optical medium 108. This image is processed within a processing unit 107, which can be directly connected to the detection device and also to the excitation transmission device, in the same way as the measurement information by the detection device 106. The processing device can also perform control tasks for the measurement. It can also be at least partially separated and remote from the remaining parts of the device and communicate with these by means of a wireless connection.

(42) The image data from the camera 130 can thus be further processed inside the housing, or via a radio link even outside the housing, and compared with a personal identity database to retrieve calibration data of the identified person.

(43) This type of calibration data can also be stored for remote retrieval in a database, in one embodiment, a cloud. The measurement data from the detection device 106 can also be further processed both within and outside of the housing.

(44) If data are processed outside the housing, then the resulting data should preferably be sent back to the device within the housing by radio to be displayed there.

(45) In either case, a display can be provided on the housing 122, which advantageously can be read through the optical window, and in one embodiment also to some extent through the optical medium. The display can also project an optical indicator through the optical window onto a display surface and can have a projection device for this purpose. The display can be used in one embodiment to display a measurement or analysis result, in particular a glucose concentration. The information can be output in one embodiment via a symbolic or colour code. By means of the display or a signalling device parallel thereto, in one embodiment a proposal for an insulin dose can be presented, dependent on other patient parameters (e.g. insulin correction factor), or a signal can be transmitted automatically to a dosing device in the form of an insulin pump.

(46) The connection of the device to and from an external data processing device 131 can be implemented using all common standards, such as fibre-optic cables, cable, wireless (e.g. Bluetooth, WiFi), or else ultrasound or infrared signals.

(47) FIG. 9 shows a modulation device with a controller 132, which activates the excitation transmission device in a modulated manner. Both the controller 132 and the detection device 106 for the measuring light beam are connected to the evaluation device 107.

(48) FIG. 10 shows an excitation light source 100, in front of which a mirror device, in particular a mirror device driven by a MEMS (micro-electromechanical system) 135 is arranged, with one or more micro-mirrors 133, 134, such as those known from optical image projector technology, for the occasional deflection of the excitation light beam in a deflection direction 136.

(49) FIG. 11 shows an excitation light source 100, in front of which an optical layer 138 with a transmission that can be controlled by means of a control device 137 is arranged in the excitation light beam, in one embodiment with LCD cells.

(50) In summary, it should be noted that the device described in the present case and the described measuring method, in particular in its application to glucose measurement to patients, spares them the painful and uncomfortable invasive measurement and thereby also facilitates regular and more frequent measurement. Also, the measurement results are easily processed and the recurring costs are minimized. The measurement can be carried out without the consumption of analysis substances.

(51) The sensitivity of the measurement method easily reaches 30 to 300 mg per dl. Dependencies of the measurement results on materials other than glucose, such as alcohol or drugs in the blood, are minimal or non-existent. The measuring device can be operated without learning or training costs and measurements can be carried out over sustained periods without calibration.

(52) The following factors can be used separately or in combination when the present device and measuring method are implemented for use in glucose measurement:

(53) A spectroscopy technique in the middle-infrared is used, in which glucose has a characteristic absorption spectrum (see FIG. 14). Here, for example, the entire spectral fingerprint of glucose can be covered. A pulsed quantum cascade laser or an alternative laser light source is used, which can cover a number of characteristic wavelengths.

(54) The photothermal detection method described above is used (FIG. 15, FIG. 16).

(55) The excitation and detection are adjusted in such a way that the absorption is measured in the interstitial fluid of the skin. The laser beam (excitation beam) penetrates up to 100 microns into the skin and reaches glucose molecules in the interstitial fluid of the skin. As a result of the absorption of light and the associated energy transfer, a thermal wave is generated, which in part, travels to the skin surface where it can be detected with the photothermal detection element described above. This makes use of a detection or interrogation laser beam, the deflection of which in the optical medium depends on the heating action of the thermal wave in the optical medium. The deflection is detected as an indicator for the absorption of the excitation beam by glucose.

(56) When applied to the skin the excitation laser beam penetrates the stratum corneum, that is to say, the dead cells of the skin on the surface, which do not contain a current glucose level. The excitation beam reaches the stratum granulosum and stratum spinosum with relevant glucose components. The glucose levels in these layers directly follows the blood glucose level; the blood glucose level of interstitial fluid represents approximately 85-90% of the blood glucose level. This applies particularly to parts of the body that are well supplied with blood, such as the fingertips, thumbs, earlobes and lips. The material composition in the interstitial fluid is simpler overall than that in the blood, so that the interfering or distorting factors are lower for measurements in the interstitial fluid.

(57) Certain distortions of the measurements due to variations in the outermost skin layers can also occur from subject to subject and are also time-varying.

(58) In order to eliminate or minimize such distortions, measurement values are acquired from different skin depths (distance ranges to the skin surface). For this purpose, the infrared spectra for a plurality of modulation frequencies of the excitation beam (FIG. 17, FIG. 18) are determined and by combination of the spectra, are used to eliminate effects of upper layers of the skin.

(59) As a result, the measurement method described for measuring glucose levels can compete with the current standard invasive methods in terms of accuracy and reliability (cf. FIG. 19).

(60) FIG. 20 shows a measuring device similar to the one shown in FIG. 8, wherein the same reference numerals denote the same functional elements. This also applies to FIGS. 21, 22 and 23.

(61) In FIG. 20 various temperature sensors 150, 151 and 152 are shown, which can be implemented individually or in groups or all in one measuring device, wherein the sensor 150 measures the temperature of the excitation transmission device 100, thus for example on a laser or a laser array, the temperature sensor 151 measures the temperature of an optical medium 108 and the temperature sensor 152 the temperature of a detection device, for example a photosensor. One or more of the measured temperature values can either be taken into account in the analysis of the material, by accounting for correction coefficients for the radiation intensity of the excitation transmission device, or for the detection sensitivity of the photosensor or other parts of the detection device in the evaluation. The correction coefficients may be given in the form of a calculation formula or be stored electronically in a table. However, it can also be provided, by means of a heating element 153 which can be arranged on the excitation transmission device 100, on the photosensor or, for example, on the optical medium, to use temperature regulation to keep the measuring device, wholly or partially, at a temperature which is higher than the ambient temperature and/or than the body temperature of a patient, so that a short-term temperature change due to heating under external influence is not a cause for concern.

(62) FIG. 21 shows the use of a measuring device for measuring a urea concentration, wherein the excitation light wavelengths are selected such that they enable the detection of urea, thus for example, the absorption wavelengths of urea. The measuring can be performed on a part of the body, but also on a dialysis line 15 or a blood line of a dialysis machine. The corresponding line should then be firmly clamped to the optical medium.

(63) FIG. 22 shows a measuring device with a moisture sensor 155, which is used to determine whether an object is placed on the optical medium 108. Only in the case of increased humidity or if the moisture value is detected in a specified value window, is the excitation transmission device enabled for operation, or turned on. This is intended to avoid the excitation radiation entering the environment more than necessary, even though it is essentially harmless. The switch actuated by the sensor 155 is labelled with 156.

(64) At the same time, FIG. 22 shows a device for the suction of air 161, 162, 163, wherein 161 and 162 designate openings which end on the front of the optical medium and which are connected to a suction channel. This suction channel can extend e.g. in a circle around the region of the optical medium, which a body part is pressed against to perform a measurement. The suction openings can also be distributed in a circle. By means of the suction channel, the suction openings are connected to a vacuum suction device 163, for example in the form of a suction pump, during the operation of which an object pressed onto the optical medium is held in position or fixed there.

(65) FIG. 23 shows a fixing device, which creates a hollow in the area of the optical medium into which e.g. a finger can be inserted. Alternatively or additionally, a locking clasp 165 can also be provided, which clamps the test object in place.

(66) As shown in FIG. 23, the hollow is created by a circumferential raised edge 164, which can consist of an elastic material or a cushion, in particular an inflatable cushion. An inflatable cushion can also be provided, which can be inflated after the placement of a test object, in particular a finger, and when inflated, firmly clamps the object/finger in place. The measuring devices can be connected to a device for controlling the pressure in the cushion.

(67) FIG. 23 also shows a pressure sensor 158, which can be arranged, for example, on the rear side of the optical medium, which is opposite the front side onto which an object to be measured is pressed. The sensor 158 can have, for example, a spring with a proximity switch/distance sensor and/or a piezoelectric sensor, which generates a signal as a function of the acting pressure and/or activates a switch 160 for turning the excitation transmission device on and/or off. Parallel to this, a luminosity sensor 157 is also shown in FIG. 23, which can be designed as a photosensor and which detects whether the front of the optical medium is covered by an object. In this case, the excitation transmission device is turned on or enabled by means of the switch 159, otherwise it can be disabled.

(68) FIG. 24 shows two depth profiles recorded or determined with the method according to the invention and a device according to the invention, of the density of two substances which are located in the material/body part to be examined. The two substances are identified by excitation beams with different wavelengths/groups of wavelengths, wherein for the wavelengths for example, one or more wavelengths can be chosen, in which or in the vicinity of which absorption maxima of the substances to be identified are located. The measuring method according to the invention can be used to determine density distributions 166, 167 I(T) of the two substances as a function of the depth T, measured perpendicular to the surface. The substances will typically have identical or different density distributions. If the density distribution 166 of a reference substance is known, or only the depth T1 at which the maximum 166a or other characteristic point of the distribution 166 is located under the surface, then the density distribution 167 of the other substance or the location T2 of the maximum density of its distribution can be calibrated to this reference value.

(69) The present property rights application (as already mentioned), in addition to the subject matter of the claims and exemplary embodiments described above, also relates to the following aspects. These aspects can be combined individually or in groups, in each case with features of the claims. Furthermore, these aspects, whether taken alone or combined with each other or with the subject matter of the claims, represent stand-alone inventions. The applicant reserves the right to make these inventions the subject matter of claims at a later date. This can be done either in the context of this application or else in the context of subsequent divisional applications or continuation applications claiming the priority of this application.

(70) Other detection methods for the detection of a response signal after emission of an excitation beam may comprise: photo-acoustic detectionphoto-acoustic detection using a tuning fork or other vibration element or: a slightly modified form of photo-acoustics with an open QePAS cell (Quartz-enhanced Photo-Acoustic Spectroscopy). These methods can be used to detect pressure fluctuations/vibrations on the surface and evaluate them in the manner described above for the measured beam deflection.

(71) In principle, measured values of a phase shift of the response signal relative to a periodic modulation of the excitation beam can be used for depth profiling. (To this end, warming/cooling phases of the material surface should be more accurately evaluated with regard to their waveform or pattern.)

(72) The device described can be associated with a supply of adhesive strips for removing dead skin layers, in order to allow a maximally undistorted measurement on a human body, as well as plasters with thermal conductive paste that can be applied to the optical medium on a regular basis. The optical medium can be replaceable, given suitable fastening and adjustment of the remaining parts.

(73) To perform the measurement, the device can be provided and configured not only on a person's finger, but also on a lip or an earlobe.

(74) In some embodiments the measurement can work even without direct contact and placement of the finger or other part of the body (at a distance), resulting in a contact-free measurement.

(75) The measurement can be improved with regard to its accuracy and reliability by combination of a plurality of the measuring systems described and explained, with similar susceptibility to error.

(76) DAQ and lock-in amplifiers in the evaluation can be combined in one device and overall the evaluation can be digitized.

(77) The measuring device can also be performed on a moving surface, so that in the course of a grid measurement: excitation light source and and/or measuring light source move over the skin in a grid pattern during the measurement, which allows skin irregularities to be compensated for or even eliminated.

(78) The sensitivity of the detection device/deflection unit can be optimized by adjustment/variation of the wavelength of the probe beam/measurement light source. For this purpose, the measurement light source can be varied with respect to wavelength or else contain a plurality of laser light sources at different wavelengths for selection or combination.

(79) For the deflection of the pump/probe laser an ideal transverse mode (TEM) can be selected.

(80) The excitation transmission device, measuring light source and detector can be configured as a common array and the beams can be suitably deflected in the optical medium to concentrate the emission and reception of all beams at one point.

(81) A lens on or in the crystal of the optical medium can contribute to deflecting the measuring light beam more strongly depending on the response signal.

(82) In addition, it is conceivable to use a gap-free photodiode for the detection, and a lens could then focus the measuring light beam after its exit, to thus enable a more accurate measurement.

(83) An additional variant of the invention, in accordance with the patent claims is described in the following concept. This concept, whether taken alone, in combination with the above aspects or with the subject matter of the claims, also constitutes at least one independent invention. The applicant reserves the right to make this invention or these inventions the subject of claims at a later date. This can be done either in the context of this application or else in the context of subsequent divisional applications or continuation applications claiming the priority of this application:

(84) A concept for non-invasive blood sugar measurement by a determination of the glucose in the skin by means of excitation using quantum-cascade lasers and measurement of the thermal wave by radiant heat. On the basis of FIGS. 12 and 13 a method is described with which the concentration of the glucose or another material in the interstitial fluid (ISF) in the skin can be determined. Glucose in the ISF is representative of blood glucose and follows it rapidly in the event of changes. The method consists of at least individual steps or groups of the following steps or of the entire sequence:

(85) 1. The point on the skin 102 (in this case, the first region of the material surface), is irradiated with a beam of a quantum cascade laser, which is focused and possibly reflected at a mirror or parabolic mirror 140, and which is incrementally or continuously tuned over a specific infrared range, in which glucose is specifically absorbed. Instead of the quantum cascade laser 100, a laser array with a plurality of lasers radiating at single wavelengths can also be used. The spectral range (or the individual wavelengths, typically 5 or more wavelengths) can be in particular between approximately 900 and approximately 1300 cm.sup.?1, in which glucose has an absorption fingerprint, that is to say, typical and representative absorption lines.

(86) 2. The excitation beam designated with SA is employed continuously (CW lasers) or in pulsed mode with a high pulse repetition rate or in a modulated manner. In addition, the excitation beam is low-frequency modulated, in particular in the frequency range between 10 and 1000 Hz. The low-frequency modulation can be performed with a variety of periodic functions, in various embodiments sine-wave, square wave or sawtooth wave, or the likes.

(87) 3. Due to the irradiation of the skin the IR-radiation penetrates the skin to a depth of roughly 50-100 ?m anddepending on the wavelengthexcites specific vibrations in the glucose molecule. These excitations from the vibration level v0 to v1 return to the initial state within a very short time; in this step heat is released.

(88) 4. As a result of the heat produced according to (3) a thermal wave is formed, which propagates isotropically from the place of absorption. Depending on the thermal diffusion length, defined by the low-frequency modulation described in (2) above, the thermal wave reaches the surface of the skin periodically at the modulation frequency.

(89) 5. The periodic emergence of the thermal wave at the surface corresponds to a periodic modulation of the thermal radiation property of the skin (material surface of the sample). The skin can be described here approximately as a black body radiator, whose entire emission according to the Stefan-Boltzmann law is proportional to the fourth power of the surface temperature.

(90) 6. With a detector 139 for heat radiation, i.e., an infrared detector, i.e. a thermocouple, bolometer, semiconductor detector or similar device, which is directed at the point of the skin under irradiation, the periodic temperature increase described under (5) is recorded. It depends on the irradiation of infrared light described under (1) and (2), and on the absorption described under (3), and therefore depends on the concentration of glucose. The thermal radiation SR (in this case, the response signal) is collected by means of an optical element, in one embodiment an infrared lens or a mirror, in particular a concave parabolic mirror 141, and, in one embodiment is directed via a convex mirror 141a on to the detector 139. For this purpose a collection mirror used in one embodiment can have an opening 142, through which the collected beam is directed. A filter 143 can also be provided in the beam path, which only allows infrared radiation of a certain wavelength range to pass.

(91) 7. In processing the response signals, the modulation frequency can be specifically taken into account, for which the response signal can be processed in a lock-in amplifier 144. By analysis of the phase angle between the excitation signal and heat radiation signal (response signal) using a control and processing unit 147, the depth information relating to the depth below the surface can be obtained, from which the response signals are largely obtained.

(92) 8. The depth information can also be obtained by the selection and analysis of various low-frequency modulation frequencies as described in (2) for the excitation beam and the combination of the results for different modulation frequencies (wherein the results can also be weighted differently for different modulation frequencies). Difference methods or other calculation methods can be used for this, to compensate for the absorption of the topmost skin layers.

(93) 9. To maximise the sensitivity in the detection of the thermal radiation according to point (6), it is used over a broad spectral band for the entire available infrared range. As many regions of the Planck radiation curve as possible should be used. To make the detection insensitive to the intensive excitation radiation, the detection of the heat radiation is provided with blocking filter (notch filter) 143 for these excitation wavelengths. The wavelength range 148 transmitted through the blocking filter 143 is also apparent from the diagram of FIG. 13. Therein, the intensity of the response signal is shown both as a function of the wavelength, in a first (solid) curve 145 without an excitation beam or only with excitation radiation in non-specific wavelengths for the material to be identified (i.e. without the wavelengths where specific absorption bands of the material exist), and then in a second (dashed) curve 146 a similar curve is shown, wherein an excitation beam is irradiated which contains specific absorption wavelengths of the material to be identified.

(94) 10. From the thermal signal measured according to (6-9), which is dependent on the excitation wavelength, if glucose is to be identified, in one embodiment the background is determined first with non-glucose-relevant wavelengths (or excluding them) of the excitation beam (curve 145), and then with (or including) the glucose-relevant wavelengths the difference from the background signal is determined. This results in the glucose concentration in the skin layer or skin layers, which are defined by the selected phase position according to (7) or the different modulation frequencies according to (8) or a combination of these.

(95) Although the invention has been illustrated and described in greater detail by means of preferred exemplary embodiments, the invention is not limited by the examples disclosed and other variations can be derived therefrom by the person skilled in the art without departing from the scope of protection of the invention.

LIST OF REFERENCE NUMERALS

(96) 10 device 100 excitation transmission device/excitation light source 100a emitters/transmission elements 101 material 102 first region 103 volume 104 device 105 device 106 detection device 107 processing device/evaluation device 107a memory 108 optical medium 108a surface section 108b surface section 109 adjustment device 110 partial surface 111 partial surface 112 measuring beam/measuring light beam 113 mirror surface 114 mirror surface 116 opening 117 opening 118 opening 119 connector body 120 fibre-optic cable 121 support 122 housing 123 body 124 side 125 belt 126 fingertip 127 adjustment device 128 imaging optics 129 imaging optics 130 optical detector/camera 131 data processing device 132 controller 133 micro-mirror 134 micro-mirror 135 micro-electro-mechanical system 136 deflection device 137 control device 138 layer 139 infrared detector 140 mirror 141 parabolic mirror 142 opening in 141 143 wavelength filter 144 lock-in amplifier 145 signal curve of the response signal (solid line) 146 signal curve of the response signal (dashed line) 147 control and processing device 148 wavelength range BZA blood sugar level indication D detection result GF interface SA excitation beam SR response signal