A SYSTEM AND A METHOD FOR MEASUREMENT AND PRESENTATION OF FLUID FLOW MOVEMENTS, PARTICULARLY THE FLOW OF BLOOD THROUGH A BODY ORGAN

Abstract: The invention relates to a system and to a method for the measurement and presentation of flow movements in a fluid, particularly for determining blood perfusion in the superficial blood vessels of a body organ. The system includes a laser beam generating source (1), means (3, 6) for directing the laser beam (2) onto the body part to be examined and for moving the laser beam in a controlled fashion over the body part in accordance with a determined scanning pattern (8). This system also includes means (9) for receiving part of the laser beam reflected from the body part. Also included in the system are means (10, 7) for detecting the broadened frequency of the reflected portion of the laser beam, this spectral broadening being caused by the Doppler effect, for a large number of points along the path (8) scanned by the laser beam, this broadening of the frequency being used as a measurement of the magnitude of the superficial blood circulation in the examined body part (5) at these points.

Description: A system and a method for measurement and pre¬ sentation of fluid flow movements, particularly the flow of blood through a body organ Field of Invention The present invention relates to a system and to a method for the measurement and presentation of flow movements in a fluid, and particularly for determining the magnitude of blood perfusion through the super¬ ficial blood vessels of a body organ. The system includes a laser beam generating source, means for directing the laser beam onto the part of the body to be examined and also to control the movement of the laser beam over said body part in accordance with a predetermined scanning pattern, and means for receiving part of the laser beam reflected from said body part. Background of the Invention The invention is based on the application of the known laser-Doppler-technique for measuring the superficial circulation of blood in cutaneous tissue. This technique is described, for instance, in US 3 511 227, US 4 109 647, SE 419 678 and in the articles "In Vivo Evaulation of Microcirculation by Coherent Light Scattering", Stern N.D., Nature Vol. 254, pages 56-58, 1975; "A New Instrument for Continuous Measurement of Tissue Blood Flow by Light Beating Spectroscopy", Nilsson, G.E., Tenland T. and δberg P.A., IEE trans. BME-27, pages 12-19, l.-GO, and -"Evaulation of a Laser Dopper Flow Meter for Measurement of Tissue Blood Flow", Nilsson G.E., Tenland T. and δberg P.A. , IEE trans. BME-27, pages 597-604, 1980. In principle, this technique involves directing a laser beam onto a part of the tissue and receiving, with the aid of an ap- propriate photodetector, a part of the light scattered and reflected by that part of the tissue irradiated by the laser beam. As a result of the Doppler effect, the frequency of the reflected and scattered light will be broadened and the light will thus have a frequency spectrum which is broader than the original laser beam, this broadening of the light frequency being due to the influence of the movement of blood cells in the super¬ ficial part of the irradiated tissue. The extent to which the frequency is broadened and the light intensity within different parts of this broader frequency spectrum constitute a measurement of the magnitude of superficial blood circulation in the irradiated part of the tissue examined and can be determined or evaluated by appropriate processing of the photodetector output signal. An instrument for visually presenting blood flow is known from US-A-4,862,894. In this known instrument, the reflected laser light is detected by a line sensor consisting of a plurality of light receiving elements which emit successively signals that are converted and stored in a memory. A microprocessor makes calculations based on these stored signals. According to US-A-4,862,894, the reflected Doppler signal is evaluated by measuring the amplitude of the signal at time t and comparing the result with the amplitude of the signal at time t + Δt. Thus, the amplitude values of the Doppler signal are detected by this method, whereas the frequency content of the signal is completely icnored. Hcwr.ver, the signal processing technique and the use of the algorithm described in US-A-4,862,894 enable the technique for scanning the measurement area described in this Patent Specification to be used. Under some conditions, the signal processing technique described in US-A-4,862,894 will result in erroneous evaluation of the blood flow in a body part, since the frequency content of the Doppler signal is a component which is necessary in order to describe the blood flow correctly. Perfusion is proportional to the product of the speed and concentration of red blood cells and it is not possible to evaluate perfusion or average speed unambiguously, solely by studying changes in the ampli- tude, as proposed in US-A-4,862,894. The Basic Concept of the Invention The present invention is based on a signal processing method in which both the magnitude and the frequency of the Doppler signal are detected, which is necessary in order to obtain a correct measurement of the blood perfusion. In order to be able to evaluate the Doppler signal, it is necessary to detect the signal over a period of sufficient duration to enable all frequencies in the signal to be detected. Accordingly, the laser beam is halted at each measurement point for a given time interval, the signal being measured continuously. The present invention relates to a system for the measurement and visual presentation of the magnitude of the superficial blood circulation over an area of a body part, for instance over a complete hand or foot, or part of a hand or foot, or part of a leg. The superficial blood circulation can vary considerably within different regions of a body part, and the des¬ cribed system will therefore enable the cause of an illness or a healing process to be studied effectively. The inventive system includes a laser beam generating source, and means operative to direct the beam onto the body part to be examined and to move the beam over said body part in accordance with a determined scanning pattern. The system also includes means for receiving light reflected from said body part and for detecting the broadening in the frequency of the reflected light caused by the Doppler effect and for recording this broadening of the frequency for a large number of points along the scanning path as a measurement of the superficial blood circulation in said body part at said measurement points. The system also includes means for visually presenting on a colour screen the magnitude of the superficial blood circulation at the scanned points, with the use of mutually different colours for mutually different magnitude intervals of blood cir¬ culation. Those measurement or scanning points on the examined part of the body at which no blood circulates, or where blood circulation is only very slight, will cause no broadening of the frequency of the reflected light received, or at most only a slight broadening of the frequency. Thus, it will be impossible, or extremely difficult, to distinguish these measurements or scan¬ ning points from those measurement or scanning points which lie outside the examined part of the body. This may make it difficult to interpret correctly the image of the superficial blood circulation in various regions of the body part examined on the colour screen. This drawback is eliminated by one advantageous e bodi- ment of the invention, in that an underlay on which the examined body part is placed is configured so as to be substantially non-reflective, i.e. is either trans¬ parent or light-absorbent. The signal obtained from the detector is analyzed in the signal processing unit, not only with respect to the broadening of the signal frequency, but also with respect to the absolute value of the intensity of the reflected light received by the detector. Since the underlay is substantially non- reflective, the light reflected at the measurement or scanning points located outside the examined body part will have a very low intensity. Because all measurement or scanning points whose light intensity lies beneath a predetermined limit value are marked with a unitary background colour, a readily interpreted image is obtained on the colour screen. In the. image producing system in which the laser beam scans the measurement object, the distance between measurement object point and detector surface will vary during scanning of said body part, and therewith also the angle of the reflected beam in relation to the detector. The so-called amplification factor of the system for the signal measured will therewith vary within one and the same image, which introduces distor- tion in the reproduction of the blood flow image. In accordance with one preferred embodiment of the invention, compensation is made for those variations which occur in the output signal as a result of the relative position of the measurement point on the measurement object, so as to provide correct presenta¬ tion of the measured flow values. This compensation enables a comparison to be made between different measurements, for instance will enable a healing process to be evaluated. It is also possible to present correctly an image of a number of punctiform measure¬ ments made on a systema ically rcanned surface. Brief Description of the Drawings The invention will now be described in more detail with reference to the accompanying drawing, in which Figure 1 is a schematic illustration of an exem¬ plifying embodiment of a system for measuring and visually presenting the blood flow in a hand; Figures 2 A-D illustrate by way of example dif¬ ferent Dopper signals reflected from a measurement point as a function of time; Figure 3 illustrates by way of example a visual presentation of the superficial blood circulation of part of a hand, in accordance with the inven¬ tion; Figure 4 illustrates schematically how a measure¬ ment object is visible from a detector included in an apparatus according to Figure 1; Figure 5 illustrates schematically a speckle pattern reproduced at mutually different distances from the measurement object; Figure 6 illustrates schematically the relation- ships between different components of the Figure 4 illustration; and - Figure 7 is a diagram illustrating the flow values measured on a medium in uniform movement. Detailed Description of the Invention Figure 1 illustrates schematically a system for the measurement and visual presentation of the superficial blood flow in a hand, and comprises a laser beam generating source 1 which produces a laser beam 2. The laser beam is directed onto an underlay 4, which sup¬ ports the part of the body to be examined, with the aid of suitable optical elements, of which two mirrors 3 are shown in Figure 1. The two mirrors can be swung by means of stepping motors 6 controlled by a computer 7, also illustrated schematically. The laser beam is caused to scan the underlay 4 and the body part 5 positioned thereon in accordance with a predetermined scanning pattern 8. Scanning movement of the laser beam 2 is preferably carried out in stages, so as to obtain a plurality of scanning or measuring points located sequentially along the scanning path 8. If the laser beam 2 is assumed to have a diameter of 1 mm and the distance between the underlay 4, with the body part 5 resting thereon, and the scanning unit, i.e. the mirrors 3, is assumed to be about 20 cm, and the measurement points or scanning points are 3,600 in number, an area of 12 x 12cm 2 can be covered with one single scanning procedure. When the laser beam 2 im- pinges on the body part 5, the beam will be scattered and reflected in the superficial tissue and therewith also to some extent by the blood cells in the superfi¬ cial or cutaneous blood circulation in the measurement point concerned on said body part. Some of the scat- tered and reflected light is captured by a photo¬ detector 9, of some suitable kind, and the photodetec¬ tor output signal is delivered to a schematically illustrated signal processing unit 10. The frequency of the light received by the photodetector 9 is broader than the frequency of the original beam 2, this broadening of the frequency with respect to its mag¬ nitude and also with respect to the variations in light intensity in different parts of the frequency spectrum constitutes a measurement of the superficial blood circulation at the measurement point concerned on the body part 5 under examination. In order to be able to record both magnitude variations and frequency broadening in the reflected light, it is necessary for the laser beam to remain stationary at each measurement point for a period of time sufficient to enable all frequencies of the signal to be detected. It has been found that the laser beam must remain stationary for at least 20-30 milliseconds, in order to achieve satisfac¬ tory signal detection. Figures 2 A-D illustrate Doppler signals which occur at different combinations of speed and concentration of red blood cells for one and the same perfusion or blood flow. This perfusion or blood flow is proportional to the product of the speed and the concentration of red blood cells in the measurement area. Figure 2 shows how- the frequency of the Doppler signal is proportional to the mean speed of the blood cells, provided that the concentration is constant, whereas the magnitude for a given speed is related to the concentration. It will also be seen from Figure 2 that the magnitude decreases with increasing speed for a given concentra¬ tion (see, for instance, Figures A-B) . This is because the energy in the Doppler signal is now distributed over a larger frequency range (lower concentration for each speed interval) . Thus, a high perfusion can be corresponded by a low signal magnitude when it is the speed component that increases and not the concentration. In actual fact, a reversed condition between magnitude and mean speed prevails, provided that perfusion is constant. Conse¬ quently, it is not possible to determine perfusion or mean speed unambiguously, by solely studying amplitude changes. Figures 2 (A and D) illustrate a situation in which the mean flow rate is low (A) and the concentra¬ tion is also low (D) , and a comparison of these Figures will reveal that changes in signal amplitude at two mutually sequential measurements cannot be proportional to the mean speed (high mean speed in D and low ampli¬ tude and amplitude difference; low mean speed in A and high amplitude and amplitude difference) . Thus, a measurement of the magnitude of the superficial blood circulation is determined for each measurement point on the body part 5 being examined, by appropriate processing of the photodetector output signal in the signal processing unit 10. These measurement values are delivered to and stored in the computer 7 for all measurement points along the scanning path 8 of the laser beam 2. The computer 7 is connected to a colour monitor 11 on which an image of the body part 5 being examined is presented visually. Each individual measurement point in this image is shown in a specific colour corresponding to the range of magnitude within which the superficial blood circulation in corres¬ ponding measurement points on said body part lies. This produces a graphic, highly informative picture of the • superficial blood circulation in the body part being examined. Because. the absolute values of the super- ficial blood circulation in each measurement point on the body part being examined are stored in the computer 7, it is possible to select, with the aid of the computer 7, the different size intervals for the various colour codes in the image on the colour monitor 11, so as to obtain the best possible, informative visual presentation with each individual examination. It will be evident from the aforegoing that at those measurement or scanning points on the examined body part 5 where blood circulation is non-existent or very low, there will be no broadening or a very slight broadening of the frequency of the reflected light received by the photodetector 9, and, consequently, it will be impossible or extremely difficult to dis¬ tinguish these measurement or scanning points on the body part 5 from those measurement or scanning points which lie outside the examined body part 5. This may render it difficult to interpret correctly the image of the superficial blood circulation in different parts of the examined body part presented on the monitor 11. This drawback is eliminated in accordance with one highly advantageous embodiment of the invention, by configuring the underlay 4, on which the examined body part 5 rests, in a manner such that the underlay will essentially reflect no light, i.e. by making the under¬ lay either transparent or light absorbent, and by analyzing the photodetector output signal in the signal processing unit 10 solely with respect to the frequency broadening of said signal without taking into consi¬ deration its absolute value, i.e with respect to the intensity of the reflected light received by the photo¬ detector 9, and by storing in the memory of the computer 7 the intensity values of the reflected light received for each measurement or scanning point along the whole of the scanning path 8. Thus, subsequent to each scanning process, two "images" are found stored in the memory of the computer 7, of which "images" one represents the magnitude of the superficial blood cir- culation in each scanning or measurement point, and the other "image" represents the intensity of the light reflected from each scanning or measurement point. Since the underlay 4 is essentially non-reflective, it will be realized that this latter "image" presents a very low intensity of the light reflected from the measurement or scanning points which lie outside the examined body part. These two "images" stored in the computer 7 can be used to produce on the monitor 11 a visual presentation of an image or a picture in which all measurement or scanning points, i.e. picture pixels, which have a reflected light intensity beneath a predetermined limit value are marked with a unitary background colour, whereas only those measurement or scanning points, i.e. picture pixels, which have a reflected light intensity that lies above said limit value are marked with a colour representing a given size interval for the superficial blood circulation. The picture presented on the monitor in this way is far more informative and much more readily interpreted than is otherwise the case. Naturally, when producing the picture on the colour monitor, the magnitude of the aforesaid limit value of the reflected light intensity during which background colours are used can be selec¬ ted in accordance with prevailing requirements. Figure 3 is an exemplifying illustration of a picture (in black and white) produced in the aforedescribed manner and showing the superficial blood circulation in part of a hand. In this picture, the background, i.e. the area outside the outer contours of the hand, is marked with a mauve or purple colour, whereas the various size ranges of the superficial blood circula¬ tion in the hand are marked in sequence in black, blue, green, yellow and orange colours in the case of progressively greater superficial blood circulation. The hand examined in the illustrated example carried a ring on one finger, and the ring appeared on the pic¬ ture as a black band over the finger concerned, while another finger was provided with an occlusion which cut-off the superficial or cutaneous blood circulation in the outermost part of said finger. This is shown clearly in the picture, where said outermost part of the finger concerned shows up black. Figure 4 illustrates the laser beam 2 directed onto the skin surface 5 where the flow of blood is to be mea¬ sured, wherein a Doppler shift of certain photons in the laser beam takes place and gives rise to a frequency broadening and also in variations in the intensity of the light reflected. These variations in intensity are recorded with the aid of a photodetector 9, which is preferably located at a distance of about 20 cm from said skin surface, and are converted to a signal which is proportional to the blood flow. When laser light is scattered in a medium, the scat- tered light consists of Doppler-broadened light, the intensity variations of which, mirrored for instance on a white screen, are represented by a so-called laser speckle, as illustrated in Figure 5. When light emitted by a light source of given geometrical extension (such as the end of an optic fibre) is incident on a surface (such as the surface of a photodetector) , there is formed a defraction pattern (speckle) whose appearance is contingent on the physical extension of the light source, the distance between the light source and the photodetector surface, and the wavelength of the light emitted. When the medium, on which the light impinges is in motion, such as red blood cells which perfuse a tissue, this speckle will constantly undergo a phase shift, i.e. will be constantly in motion ("boil" in the technical jargon used) . It is this pattern of movement which is detected by the photodetector 9 located at a given distance from the skin surface being examined, and which is converted to a signal which is proportional to the blood flow. The magnitude (fine structure) of the shifts in the speckle between dark and light fields on the detecting, photosensitive surface is designated the coherence area. Under cer¬ tain, fixed conditions, the size of the coherence area depends on the distance between the measurement object 5 and the detector 9, see Figure 6, in accordance with the formula: A coh = X , 2- I Ω ( 1 ) where λ is the wavelength of the light and Ω is the space angle 12 under which the light source is visible from the detector 9. Figure 5 illustrates the reflec¬ tion of a fine-grain speckle 13 onto a screen which lies relatively close to the measurement object 5, and also shows a coarse-grain speckle 14 reflected on a screen located at a relatively long distance from the measurement object 5. Since the size of the space angle 12 decreases with increasing distance between measurement object and detector, the size of the coherence area on the detec- tor surface according to formula (1) is contingent on this distance. Since the area of the detector surface is constant, the number of coherence areas on the detector surface will be dependent on the distance between the measurement point on the measurement object 5 and the detector 9. A greater distance results in a smaller number of coherence areas on the detector surface, while conversely a smaller distance will result in a greater number of coherence areas. When measuring blood flow with the aid of laser- Doppler-techniques, the so-called amplification factor, and therewith the size of the output signal, is contin¬ gent on the number of coherence areas which impinge on the detector surface. This relationship can be des- cribed in simple fashion by the formula: Output signal = K_ x BF/N (2) where K Q is an instrument constant, BF = the blood flow and N = the number of coherence areas on the detector surface. In conventional laser-Doppler-techniques based 15 angle of the light beam incident on the measurement object point. Figure 6 illustrates the manner in which a system compensation factor can be measured and calculated. In Figure 6: R D = detector radius R s = laser beam radius D = perpendicular distance between detector plane and - measurement object C = measurement object point at D X = distance of detector from trie measurement point concerned M = the measurement point concerned Y = distance C - M = angle D - X In order to calculate the space angle Ω, i.e. the angle at which the light source on the measurement object is visible from the detector, the light propagation of the light source is compared with the total surface area of the sphere of radius X, i.e.: π R s 2 R s n __ = ( ) 2 4τr X 2 2X The size of the coherence area can now be calculated with the aid of formula (1) . λ 2 2X 2λX Aco H = = λ 2 ( ) 2 = ( ) 2 Ω R s R s 14 on light fibres, where the blood flow is detected pointwise at a constant distance between measurement object and detector surface and a constant space angle 12 under which the light source at the fibre end is visible from the detector surface, the number of co¬ herence areas will also be constant, according to the relationship of formula (1) . The amplification factor of the system will not vary under these conditions, and, consequently, according to formula (2) , the output signal will be directly proportional to the blood flow. In other systems, on the other hand, the distance between measurement obηect and detector surface can vary between different measurement occasions, and, consequently, two images cannot be compared with res¬ pect to the absolute flow values. In the case of laser- Doppler-flow measuring techniques in which a body surface is scanned systematically and in stages, the space, angle, and therewith the number of coherence areas and the system amplification factor, will be contingent on the point on the measurement object at which backscattering of light occurs. This causes the amplification factor to vary within one and the same image and therewith introduces distorsion in the repro- duction of the flow image, unless these amplification factor variations can be corrected. For the purpose of solving this distorsion problem, an inventive method has been devised in which measurements and calculations are made of those amplification factor variations which occur at different measurement object points in relation to the amplification factor which occurs at an optimum measurement point. The size of the variations of the amplification factor, or the size of the variations in the number of coherence areas on the detector surface, is a function of the distance and the The number of coherence areas N which impinge on the detector surface can be calculated with the aid of the component of the detector radius perpendicular to the reflected beam, i.e. R n cos α. π(R D cosα) 2 N = *C0H 7T(R D cos a) 2 R s 2 R D R s cos α = 7T ( ) 2 ( 2λX ) !λX R D R s X- COS R D R s D = π ( ) - = π ( ) 2 2λX z 2λ (O +Y ) R D 2 R S 2 D = π ( ) 2 4λ 2 D 2 +Y 2 The compensation factor K can now be calculated by comparing the value of N for the optimum measurement point C. Rn e N C = IT (2λD) : N D 2 K = = ( ) 2 N c D 2 +Y 2 It will be evident from the formula by means of which the compensation factor is calculated that this factor can be calculated readily when 1) the perpendicular distance D between detector and measurement object is known, and 2) when it is known how the distance X between detec¬ tor and measurement object changes as the laser beam moves over the measurement object, or in accordance with Figure 6, when the value of the distance Y between the measurement object points C nearest the detector and the measurement point M concerned is known. The perpendicular distance D is preferably measured by sending a short ultrasonic pulse onto the object 5 from an ultrasonic crystal which is distance related to the detector plane. The time taken for this pulse to return to the crystal and there detected is related linearly to the distance D. This distance can be calculated with knowledge of the speed of sound in air. For instance, by observing the number of steps through which the motors 6 are stepped forward as the laser beam 2 scans the measurement object 5 and storing this information, it is possible to calculate the distance to each mea¬ surement object point M and to use this calculation in the calculation of the compensation factor. When con¬ tinuous motors are used for effecting rotary movement of the mirrors, there can be used instead a feedback system which is operative to detect the rotational positions of the mirrors and therewith the location of the measurement point concerned. In the case of the optimum measuring point C, the amplification factor will assume a typical value of 1 in the centre of the image, and will then increase successively out towards the perimeter edges of the image, where a typical value may be about 2. The compensation factor varies in a corresponding manner, from the optimum value 1 to a value of about 0.5. The result of an experiment performed in this regard is illustrated in Figure 7, with the intention of exempli- fying the above theoretical reasoning and in order to illustrate the significance of the amplification factor on the measurement result. In this experiment, the laser beam was swept over a medium in uniform motion (microspheres in solution) , wherein the distance between detector and measurement object point varied during the beam scan over the object. As a result of these changes in distance, the space angle 12 at which the light source is visible from the detector 9 also changed, and, consequently, the coherence area and therewith the number of"coherence areas on the detector surface also varied. In consequence, a change in the value of the amplification factor was also observed during the scan. The smallest output signal is obtained when the measurement object point is located immedi- ately beneath the detector, when Y = 0. The number of coherence areas decreases when the measurement object point is located on the peripheral edge of the image, wherein the amplification factor increases. Since the measurement is concerned with uniform motion, a horisontal flow line should be read from the diagram in Figure 7, if correction was made to the output signal with respect to the variation in the amplification factor. Figure 7 shows that compensation for ampli¬ fication factor variations is of great importance, since in the case of a non-compensated system erron¬ eously high flow values, of up to 100%, are detected, particularly at the peripheral edges of the image. The Figure also includes the theoretically calculated amplification curve foj which compensation shall be made with the aid of the compensation factor calculated in accordance with the aforegoing.

Claims: Claims 1. A system for the measurement and presentation of flow movements in a fluid, particularly for determining blood perfusion in the superficial blood vessels of a body organ, said system including a laser light source (1) for generating a laser beam (2), means (3, 6) for directing the laser beam (2) onto the body part to be examined and for guided movement of the laser beam over said body part (5) in accordance with a predetermined scanning pattern (8) , and means (9) for receiving part of the laser beam reflected from the body part, charac¬ terized in that the system further includes means (10, 7) for detecting, over a large number of points along the path (8) scanned by the laser, broadening of the frequency of the received reflected light beam caused by the Doppler effect, as a measurement of the magni¬ tude of the superficial blood circulation in the ex¬ amined body part (5) at said points. 2. A system according to Claim 1, characterized in that the system includes means (11) for producing on a colour screen a visual presentation of the magnitude of the superficial blood circulation at the scanned points, with the aid of different colours for mutually different blood circulation magnitude intervals. 3. A system according to Claim 2, characterized in that the.system includes an essentially non-reflective underlay (4) on which the body part (5) to be examined is placed, and means (10, 7) for detecting the intensity of the received reflected light and recording the value of this intensity for each point along the scanning path (8) of the laser beam, and in that the means for producing said visual presentation is con¬ structed to mark on th colour screen those scanning points at which the intensity of the received reflected light does not exceed a given limit value with a colour which distinguishes from those colours used to mark the different magnitude intervals of the superficial blood circulation. 4. A system according to Claim 3, characterized in that the underlay (4) is transparent or light absor¬ bent. 5. A system according to Claim 1, characterized in that the means (9) for receiving part of the laser beam reflected from the body part comprises a detector having a detector surface which defines a detector plane; and in that means are provided for detecting the distance (D, X) from the centre of the detector plane to the measurement point (C) on tne measurement object positioned perpendicularly to the detector plane, or to the measurement pont (M) concerned. 6. A system according to Claim 5, characterized in that the means for detecting the perpendicular distance between the detector plane (9) and the measurement point (C) includes an ultrasonic crystal which is stationarily mounted in relation to the detector. 7. A method for measuring and presenting flow move¬ ments in a fluid, particularly for determining the blood perfusion in the superficial blood vessels of a body organ, characterized by directing a laser beam (2) , generated by a laser beam source (1) , onto a measurement object (5) in the form of a body organ which scatters and reflects the light beam; receiving and detecting the reflected light in a detector (9) and detecting the broadening in frequency caused by the Doppler effect; compensating the output signal of the detected frequency broadening with a compensation factor (K) contingent on the space angle (12) within which the laser beam source is visible from the detec¬ tor (9) at the measuring point (M) concerned on the measurement object (5) . 8. A method according to Claim 7, characterized in that the compensation factor (K) ά≤ contingent on the distance between the detector (9) and the measurement point concerned and the angle of the reflected beam in relation to the detector plane. 9. A method according to Claim 7 or 8, characterized in that the compensation factor (K) is determined by measuring the perpendicular distance (D) between the centre of the detector plane (9) and a point (C) on the measurement object (5) , and by also measuring the distance (Y) between said point (C) and the measurement point (M) concerned on the measurement object (5) . 10. A method according to Claim 9, characterized by moving the laser beam (2) over the measurement object (5) in a determined scanning pattern, such that the detector (9) will receive and detect the light reflec- ted from a large number of measurement points (M) along the scanning path; and by determining the compensation factor (K) for each of these measurement points (M) . 11. A method according to Claim 10, characterized by moving the laser beam (2) with the aid of rotatable optic elements (3) which are rotated with the aid of stepping motors (6) ; and by determining the compensa¬ tion factor (K) by measuring the perpendicular distance (D) between the centre of the detector plane (9) and a point (C) on the measurement object (5) and by measur¬ ing the number of steps moved by the stepping motors (6) from the position at which the laser beam was directed onto said point (C) to the measurement point (M) concerned. 12. A method according to any one of the preceding Claims, characterized by calculating the compensation factor (K) in accordance with the formula D 2 K = ( ) 2 , where D 2 + Y 2 D = the perpendicular distance (D) between the detector plane (9) and the measurement object (5) , and Y = the distance between the measurement object point (C) at D and the measurement point (M) concerned. 13. A method according to Claiύi 12, characterized in that the compensation factor (K) takes the value 1 at a prevailing measurement point (M) which corresponds to the measurement point (C) at a perpendicular distance from the centre of the detector plane (9) and decreases successively for prevailing measurement points (M) that are located further out towards the peripheral edges of the measurement object (5) . 14. A method according to Claim 13, characterized in that the compensation factor (K) takes values between 1 and about 0.5.

Inventors: NILSSON GERT, NILSSON, GERT
Applicants: NILSSON GERT, NILSSON, GERT
Application year: 1990
Main classification: A61B5
IPC codes: A61B5, G01P5