WO1999004683A1 - Procede pour evaluer une repartition de lumiere diffuse obtenue consecutivement a une transillumination locale d'un etre vivant, par determination de caracteristiques - Google Patents

Procede pour evaluer une repartition de lumiere diffuse obtenue consecutivement a une transillumination locale d'un etre vivant, par determination de caracteristiques Download PDF

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Publication number
WO1999004683A1
WO1999004683A1 PCT/DE1998/001885 DE9801885W WO9904683A1 WO 1999004683 A1 WO1999004683 A1 WO 1999004683A1 DE 9801885 W DE9801885 W DE 9801885W WO 9904683 A1 WO9904683 A1 WO 9904683A1
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WO
WIPO (PCT)
Prior art keywords
characteristic values
function
scattered light
parameters
determined
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PCT/DE1998/001885
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German (de)
English (en)
Inventor
Klaus Abraham-Fuchs
Jürgen BEUTHAN
Viravuth Prapavat
Gerhard Müller
Original Assignee
Siemens Aktiengesellschaft
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Filing date
Publication date
Application filed by Siemens Aktiengesellschaft filed Critical Siemens Aktiengesellschaft
Priority to EP98943651A priority Critical patent/EP1014849A1/fr
Priority to DE19880997T priority patent/DE19880997D2/de
Publication of WO1999004683A1 publication Critical patent/WO1999004683A1/fr

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Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/45For evaluating or diagnosing the musculoskeletal system or teeth
    • A61B5/4528Joints
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/02Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/024Detecting, measuring or recording pulse rate or heart rate
    • A61B5/02416Detecting, measuring or recording pulse rate or heart rate using photoplethysmograph signals, e.g. generated by infrared radiation

Definitions

  • the invention relates to a method for evaluating a scattered light distribution obtained as a result of local radiation of a living being by determining the characteristic value.
  • pathological tissue changes caused by metabolism in a simple and as stress-free manner as possible for the patient.
  • An example of such pathological tissue changes is represented by rheumatic joint changes or rheumatic diseases in the area of the soft tissue.
  • fluoroscopy methods include, for example, the “time Of-flight "method. In this method, the tissue to be examined is illuminated with a few picoseconds of laser light.
  • the emerging photons are then recorded on the opposite side and their temporal progression is assessed, ie here the flight time of the This is based on the idea that the longer the scattering centers, which are generated, among other things, by a pathological change in the illuminated tissue, on which the photons are scattered, the longer the flight time will be at this al
  • the time-domain method which assesses the temporal behavior of the photon flux, is on the one hand the extremely complex radiation and detection unit, since the laser control must generate a light pulse in the picosecond range, and the detection unit must also be designed to detect very short radiation times. To be used as a simple and for example on a clinical scale- this time-of-flight procedure is not designed for the procedure.
  • Another method that works on the basis of the fluoroscopy of an examination object is the photon density wave method, which is a frequency domain method.
  • the laser light irradiated over a longer period of time is intensity modulated in the range of approx. 100 MHz.
  • the modulated light experiences an amplitude attenuation and phase shift, these values being the basis for the evaluation.
  • Each modulation frequency only corresponds to a certain time window, i.e. only a certain time of flight of the photons. To obtain a meaningful result, it would be necessary to work with several modulation frequencies, which would be extremely complex and too complicated for clinical use.
  • the double integrating sphere measuring technique is also known, which is a so-called continuous wave method, that is to say a continuous radiation method.
  • the tissue volume to be examined is irradiated and the radiation power of the collimated and diffuse transmission and the diffuse reflection is considered. Since this method can only be used on specimens, but not on living beings themselves, because there are morphologically related inhomogeneities (behavior, bones, etc.), this method is not suitable for an in vivo investigation.
  • a spectroscopy method is known from US Pat. No. 5,452,723, which is used in the context of spectroscopy of human tissue. With the method described there, the distortions of the measured values obtained when examining a thick tissue several millimeters thick are intended to be caused by the increased number of scattering centers of the thick tissue compared to the spectroscopy of a very thin, only a few micrometers thick tissue, in which there are fewer scattering centers influencing the measurement result, are compensated for. This is done in such a way that first a spectrum of the diffuse reflectance is recorded, then the spectrum to be "equalized", for example the fluorescence spectrum. An effective reflectance function is then determined on the basis of probability functions.
  • the equalized fluorescence spectrum is then recorded by dividing the The fluorescence spectrum is determined by the effective reflectance spectrum described on the basis of the effective reflectance function
  • the distortions of the spectrum of the thick tissue resulting from scattering and absorption effects as well as the geometry and the interface conditions are eliminated, the spectrum course obtained corresponds to that of a thin tissue to a good approximation.
  • the "equalized" measurement curve obtained is then compared with known reference curves and the best fit curve is determined, which is then investigated with regard to the presence and concentration of reference fluorofores What is the basis for the diagnosis of the corresponding tissue properties is sought.
  • the invention is therefore based on the problem of specifying a method which allows the tissue-optical conditions to be evaluated in a simple manner in order to extract characteristic values therefrom which can be made available to the examining doctor and on the basis of which he receives information which is obtained from diagnostically usable.
  • the invention is based on the fact that changes in structure and density which occur in the event of a disease lead to a change in the optical behavior of the examination object, and thus cause significant changes in the light propagation in the affected tissue volumes. These changes in the light propagation result in scattered light distributions which depend on the state of the tissue volume, ie a different scattered light distribution is to be expected from a healthy tissue than from a diseased tissue.
  • the tissue to be examined is illuminated with an (approximately) punctiform light beam, preferably with radiation in the wavelength range of the optical tissue window. When the tissue penetrates, the point-shaped light is scattered. The spatial distribution of the scattered light is detected with a flat or linear arrangement of light detectors.
  • the intensity of the scattered light measured in this way as a function of the location of the light detectors is referred to below as a scattered light distribution function, or more specifically also as a (point) blurring function.
  • the course of this wash function depends on the composition of the irradiated tissue, and thus on the chosen irradiation location.
  • function-specific characteristic values are to be determined which describe the washing function, which are therefore characteristic of the respective function.
  • Wash function is referred to, for example, Eugene Hecht, "Optik”, Addison-Wesley-Verlag, 1989, pp. 512 ff.
  • the characteristic values are determined on the basis of one or more parameterizing approximation functions, the parameters themselves representing the characteristic value (s).
  • Approximation functions which can be represented mathematically and analytically are calculated for determining characteristic values of the function course, the mathematical parameters of which characterize the function course and are suitable for a further evaluation of the measured value series.
  • Such a description of a course of a function or a series of measured values by means of a set of characteristic parameters is generally called “parameterization” of a function.
  • the wash function is parameterized by approximation with one or more, in particular three, Gaussian functions, the parameters of which then represent the characteristic values, with three parameters being extractable for each Gaussian function.
  • Gaussian functions are available in the present case since the scattered light distribution is also Gaussian, in particular in the event that the washer function represents a point washer function.
  • the invention also provides a second inventive method which can be used as an alternative to the above-described method, or in addition to this.
  • this method according to the invention (alternatively or additionally), section parameters in the form of location-related section lengths of characteristic areas of the washing function are determined as further characteristic values. That is, the blurring function, its intensity along the ordinate and its location-based position along the abscissa. is worn, its location-dependent behavior is assessed on the abscissa, although this can of course be assessed accordingly in both the one-dimensional and the two-dimensional case. It has been found in the course of investigations that the scattered light distributions, depending on the state of the tissue, also show considerable differences in their location-related behavior or course, the form of the determination of the characteristic values according to the invention being an extremely simple determination method.
  • symmetry parameters of the wash function can be determined according to the invention as further characteristic values, these parameters representing the course and the symmetry behavior of the wash function.
  • the section parameters, and possibly the symmetry parameters can be determined based on the wash function obtained directly.
  • the wash function is noisy or difficult to evaluate, it has proven to be expedient if the wash function is at least partially smoothed or if an approximately parameterized wash function is determined, i. that is, it is also possible to work with the approximation functions described with regard to the first method variant.
  • the approximation functions that can be used here can also be generated by means of one or more Gaussian functions.
  • the section parameters are characteristic abscissa sections.
  • the characteristic areas are defined by means of the turn tangent (s) that can be applied to the wash function.
  • the higher-order moments can be used as symmetry parameters, these expediently being used as normalized central moments, in order thereby to become independent of the position of the scattered light distribution and to enable comparability. It has proven to be sufficient if the zero to fourth order moments are determined.
  • the characteristic values can be determined both for a one-dimensional and a two-dimensional view of the scattered light distribution, which is expediently a point-washing function, the computational outlay for one-dimensional view being somewhat less with regard to the amount of data to be processed is.
  • scattered light distributions are evaluated according to characteristic values, these scattered light distributions being generated by the photon flux or the photon scattering behavior in the irradiated tissue.
  • the wavelength of the incident light in particular the laser light, also has a not inconsiderable influence on the scattered light behavior.
  • the current examination area has been irradiated with light of two different wavelengths, for example, the
  • the characteristic values at different wavelengths within the optical tissue window scattered light distributions of the same living being and with the same irradiation location are processed together, so that the diagnosing doctor still further information-providing and wavelength-specific characteristic values can be made available.
  • the evaluation basis for the subsequent diagnosis, into which the doctor can add for example, patient-specific diagnostic features such as age, health status, etc., can be interpreted even more broadly and well.
  • the invention further relates to a device for carrying out at least one of the above-described methods, the device having at least one radiation source, at least one radiation detector and an evaluation device which processes the data supplied by the radiation detector and has an associated display device.
  • This device according to the invention is characterized in that the evaluation device is designed to carry out at least one of the methods according to one of the preceding claims and to display the result of the determination on the display device.
  • the evaluation device has a memory device in which comparison characteristic values that are compatible with the determined characteristic values are stored, which can optionally be output together with the determined characteristic values.
  • FIG. 1 is a schematic diagram of a device according to the invention for carrying out one or both methods according to the invention
  • FIG. 2a shows a top view as a partial view of a finger joint to be examined as a schematic diagram below
  • Fig. 3 shows two examples of approximation functions to respective scattered light distributions, one of which
  • FIG. 1 shows an examination device according to the invention in the form of a schematic diagram.
  • This comprises an irradiation device 1 with a radiation source 2, for example in the form of a laser, which emits laser light with a wavelength of 675 nm.
  • a radiation detector 3 by means of which the scattered light distribution is recorded.
  • the object to be examined is brought between the illumination device 1 and the radiation detector 3, in the example shown a finger 4, the object under examination being the finger joint 5.
  • the radiation source 2 the laser light is applied to the one to be examined as a continuous light
  • the light penetrates into the examination volume and is scattered there accordingly, the optical behavior, in particular the absorption and scattering behavior, determining the shape of the scattered light distribution obtained.
  • the optical behavior between a healthy tissue and a diseased tissue can change considerably, whereby the skin and the bones in the joint shown essentially always show a constant behavior, whereas the joint capsule and the synovial fluid change with increasing rheumatic disease.
  • the detected local scatter distribution is processed in an evaluation device 6 to determine the required characteristic values, wherein the characteristic values can be output on a display device 7, for example a monitor or the like.
  • the evaluation device has a memory device 8 in which corresponding characteristic values or also comparison characteristic values can be stored, which can also be output on the display device 7.
  • 1 also shows a positioning device 9 communicating with the evaluation device 6, which can also take over the device control at the same time, by means of which it 1 1
  • FIG. 2a now shows a plan view of a finger in the form of a schematic diagram, the internal bones and the joint capsule being shown with dash-dot lines.
  • the outside of the finger consists of skin tissue 10. Inside there are the joint bones with cartilage tissue 11, between which the joint gap 12 is.
  • the joint gap 12 is surrounded by the joint capsule 13 and also contains the joint fluid 14.
  • the laser beam is now directed onto this joint, the optimal irradiation location being at point 15 in the example shown. If irradiation is now carried out at location 15, the scattered light distribution shown by way of example in FIG. 2b is determined in the one-dimensional case of observation on the detector side.
  • the normalized irradiance E (x) is plotted along the ordinate and the location around the irradiation location along the abscissa, the irradiation location 15 being at the coordinate zero point.
  • the abscissa runs perpendicular to the joint gap 12, as indicated by the scanning system of the detection in FIG. 2a.
  • the scattered light distribution is essentially bell-shaped. It represents a location-dependent point washing function when a defined input signal is implemented in the sense of a point function.
  • FIG. 3 shows two such point-washing functions in an exemplary form, the normalized irradiance being plotted along the ordinate and the location along the abscissa.
  • Curve 16 is obtained when examining a healthy joint
  • curve 17 is obtained when examining a sick joint.
  • the fluoroscopic tissue degrades; that is, it contains considerably more absorption and scattering centers, so that the photon flux passing through is less, which is expressed in the significantly changed scattered light distribution.
  • the point-washing function obtained is expediently parameterized by means of three Gaussian functions in order to generate an approximation function.
  • the approximation function (discrete function) is as follows:
  • Equation 1 w (x k )
  • the power density-equivalent variables are converted into a local irradiance distribution using a wavelength-dependent calibration function.
  • the irradiance is then normalized to the radiation power of the radiation unit in order to become independent of the input signal.
  • Such normalized approximation functions are shown in FIG. 3 as described for a healthy and a sick examination object. Using the approximation functions shown, it is already possible to determine the first characteristic values that describe the respective functions and give an evaluation criterion for the course and thus the information content of the respective function. These parameters are, cf.
  • Equation 1 the Gaussian function parameters w A j_, w B i, w C j_, where A i denotes the maximum of the distribution of the respective Gaussian function, w B i is a parameter for the width of the Gaussian function, and w ⁇ i is a measure of the displacement of w A j_ with respect to the irradiation location.
  • a i denotes the maximum of the distribution of the respective Gaussian function
  • w B i is a parameter for the width of the Gaussian function
  • w ⁇ i is a measure of the displacement of w A j_ with respect to the irradiation location.
  • the table below shows how meaningful these parameters are, in which the three parameters for the curves 16 and 17 were determined, the approximation functions being formed by means of three Gaussian functions.
  • the parameters for each Gaussian function are indicated by indices 1, 2, 3.
  • the parameters of the respective Gaussian function show considerable deviations for the sick and healthy case. This shows that these parameters represent the actual information content of the respective point washing function or approximation function well and consequently represent a sufficiently good description of the state of the curve that can be used by the doctor in the context of his subsequent diagnosis. If an unknown tissue is now examined, these parameters shown can be determined and displayed to the doctor.
  • FIG. 4 shows a basic sketch of a scattered light distribution or an approximation function, on the basis of which the generation and position of the section parameters, which likewise represent meaningful characteristic values, can be shown.
  • the turning tangents 19, 20 are applied to the two legs on the curve 18 shown. These turning tangents serve to define the section parameters arranged on the abscissa.
  • the scattered light distribution shown - based on the ordinate - can be split into three areas, namely an edge area 21, 21 ', a transition area 22, 22' and an area 23, 23 'close to the axis.
  • the widths of these areas on the abscissa define the respective section parameters.
  • the edge areas are defined on the basis of the intersection of the turning tangent with the abscissa and the point at which the spatial function runs into the abscissa.
  • the transition areas are in turn defined by the intersection of the turning tangent with the abscissa and the point at which the turning tangent reaches the functional maximum.
  • the remaining area to the ordinate represents the area close to the axis, which is usually not evaluated, but can be evaluated equally.
  • the transition areas and the border areas characterize the degree of administration 15
  • the size of the transition region is essentially characterized by the signal drop. Since the scattered light distribution is asymmetrical, a distinction is made between the proximal (towards the finger trunk) and the distal (towards the finger tip) transition area and edge area. This too
  • Characteristic values which naturally change depending on the respective scattered light distribution and thus on the condition of the tissue, represent extremely meaningful characteristic values for evaluating and describing the local function. Examples of this section parameter for a healthy and for a sick patient will be given later.
  • symmetry parameters are preferably determined as further characteristic values, which take into account, among other things, the symmetry properties of the function to be evaluated in each case. These symmetry parameters are the higher order moments of the respective function.
  • the object to be characterized should be in segmented (discrete) form as image w (x k ).
  • the moments of a discrete function w (x k ) are defined as
  • the total irradiance is calculated as follows:
  • the focus is:
  • the standard deviation is a measure of the width of the distribution. It is calculated as:
  • the skewness is a measure of the skewness of the scattered light distribution and represents the third central moment. So that distributions can be compared in different scales, the standardization is done with regard to the standard deviation s.
  • the relative skewness is calculated as:
  • the fourth central moment, the relative kurtosis is calculated as a measure of the steepness and curvature of the scattered light distribution.
  • the standard deviation s is also standardized.
  • the relative kurtosis is 3. It is calculated as:
  • the symmetry characteristic group W contains the previously described higher-order moments and additionally the characteristic value E max , which indicates the maximum irradiance.
  • the section of characteristic values contains the four specific characteristics also described above.
  • the respective characteristic values for a healthy and sick patient, to whom, for example, the approximation curves shown in FIG. 3 can be assigned differ considerably. that is, these parameters are also suitable for evaluating the information content.
  • Characteristics s, X p ü and ⁇ determined. In the case of this data reduction, only these characteristics are shown below.
  • the doctor can then make the diagnosis with the inclusion of further diagnostically usable information such as the patient's state of health, age, etc., for example also with the inclusion of further examination results using other methods.
  • the corresponding characteristic values can of course also be determined at other wavelengths, and in the course of data reduction the resulting output characteristic group can also be composed of characteristic values which were determined at different wavelengths.

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Abstract

L'invention concerne un procédé pour évaluer une répartition de lumière diffuse obtenue consécutivement à une transillumination locale d'un être vivant, par détermination de caractéristiques. Selon ce procédé, une région de l'être vivant est tout d'abord transilluminée en un point déterminé, avec un rayonnement lumineux présentant une longueur d'onde de préférence dans la plage de la fenêtre de tissu optique pour permettre l'acquisition de la répartition de lumière diffuse. Cette répartition est ensuite acquise sous forme d'une réponse impulsionnelle d'après laquelle des valeurs caractéristiques d'une ou plusieurs propriétés de la réponse impulsionnelle sont déterminées par calcul sur la base de l'allure de la réponse impulsionnelle. Ces valeurs caractéristiques servent de base pour l'évaluation. Une fonction d'approximation servant à paramétrer la réponse impulsionnelle est formée pour la détermination des valeurs caractéristiques, fonction dont les paramètres représentent la ou les valeurs caractéristiques et/ou des paramètres de segments sont déterminés en tant que valeurs caractéristiques supplémentaires éventuelles, sous la forme de zones de la réponse impulsionnelle qui caractérisent des longueurs de segments se rapportant à un point d'examen.
PCT/DE1998/001885 1997-07-21 1998-07-08 Procede pour evaluer une repartition de lumiere diffuse obtenue consecutivement a une transillumination locale d'un etre vivant, par determination de caracteristiques WO1999004683A1 (fr)

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Application Number Priority Date Filing Date Title
EP98943651A EP1014849A1 (fr) 1997-07-21 1998-07-08 Procede pour evaluer une repartition de lumiere diffuse obtenue consecutivement a une transillumination locale d'un etre vivant, par determination de caracteristiques
DE19880997T DE19880997D2 (de) 1997-07-21 1998-07-08 Verfahren zur Bewertung einer infolge einer lokalen Durchstrahlung eines Lebewesens erhaltenen Streulichtverteilung durch Kennwert-Ermittlung

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DE19731252.7 1997-07-21
DE19731252 1997-07-21

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Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE10004989B4 (de) * 2000-02-04 2006-11-02 Siemens Ag Verfahren und Vorrichtung für die Arthritis-Diagnose
WO2009022003A1 (fr) * 2007-08-14 2009-02-19 Mivenion Gmbh Dispositif et procédure de diagnostic ou de préparation au diagnostic et/ou de surveillance de thérapie de maladies inflammatoires telles que la polyarthrite rhumatoïde
WO2009147560A2 (fr) * 2008-05-26 2009-12-10 Koninklijke Philips Electronics N.V. Procédé de détection optique et dispositif de détection optique de l'état d'articulations
WO2010044003A2 (fr) * 2008-10-13 2010-04-22 Koninklijke Philips Electronics N.V. Dispositif et procédé pour examiner optiquement l’intérieur d’un milieu turbide
WO2010061339A1 (fr) * 2008-11-26 2010-06-03 Koninklijke Philips Electronics N.V. Dispositif et procédé d'examen optique de l'intérieur d'un milieu trouble

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0586025A2 (fr) * 1992-07-06 1994-03-09 Robinson, Mark R. Mesure fiable et non-invasif de gaz sanguins
US5441053A (en) * 1991-05-03 1995-08-15 University Of Kentucky Research Foundation Apparatus and method for multiple wavelength of tissue
US5452723A (en) 1992-07-24 1995-09-26 Massachusetts Institute Of Technology Calibrated spectrographic imaging
WO1996041151A1 (fr) * 1995-06-07 1996-12-19 Masimo Corporation Systeme de controle de la glycemie

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5441053A (en) * 1991-05-03 1995-08-15 University Of Kentucky Research Foundation Apparatus and method for multiple wavelength of tissue
EP0586025A2 (fr) * 1992-07-06 1994-03-09 Robinson, Mark R. Mesure fiable et non-invasif de gaz sanguins
US5452723A (en) 1992-07-24 1995-09-26 Massachusetts Institute Of Technology Calibrated spectrographic imaging
WO1996041151A1 (fr) * 1995-06-07 1996-12-19 Masimo Corporation Systeme de controle de la glycemie

Cited By (12)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE10004989B4 (de) * 2000-02-04 2006-11-02 Siemens Ag Verfahren und Vorrichtung für die Arthritis-Diagnose
WO2009022003A1 (fr) * 2007-08-14 2009-02-19 Mivenion Gmbh Dispositif et procédure de diagnostic ou de préparation au diagnostic et/ou de surveillance de thérapie de maladies inflammatoires telles que la polyarthrite rhumatoïde
CN101842045A (zh) * 2007-08-14 2010-09-22 米韦林有限公司 用于诸如类风湿性关节炎的炎症性疾病的诊断或诊断制剂和/或治疗监测的装置和方法
EA017988B1 (ru) * 2007-08-14 2013-04-30 Мивенион Гмбх Устройство и способ диагностики или диагностической подготовки и/или контроля за лечением воспалительных заболеваний, таких как ревматический артрит
US8750968B2 (en) 2007-08-14 2014-06-10 Mivenion Gmbh Device and procedure for the diagnosis or diagnostic preparation and/or therapy monitoring of inflammatory diseases such as rheumatoid arthritis
WO2009147560A2 (fr) * 2008-05-26 2009-12-10 Koninklijke Philips Electronics N.V. Procédé de détection optique et dispositif de détection optique de l'état d'articulations
WO2009147560A3 (fr) * 2008-05-26 2010-01-28 Koninklijke Philips Electronics N.V. Procédé de détection optique et dispositif de détection optique de l'état d'articulations
US10791932B2 (en) 2008-05-26 2020-10-06 Demcon Hemics B.V. Optical detection method and device for optical detection of the condition of joints
WO2010044003A2 (fr) * 2008-10-13 2010-04-22 Koninklijke Philips Electronics N.V. Dispositif et procédé pour examiner optiquement l’intérieur d’un milieu turbide
WO2010044003A3 (fr) * 2008-10-13 2010-06-10 Koninklijke Philips Electronics N.V. Dispositif et procédé pour examiner optiquement l’intérieur d’un milieu turbide
CN102246023A (zh) * 2008-10-13 2011-11-16 皇家飞利浦电子股份有限公司 用于以光学方式检查混浊介质内部的设备和方法
WO2010061339A1 (fr) * 2008-11-26 2010-06-03 Koninklijke Philips Electronics N.V. Dispositif et procédé d'examen optique de l'intérieur d'un milieu trouble

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DE19880997D2 (de) 2000-04-27

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