Apparatus for measuring blood flow

Abstract: An apparatus for measuring blood flow comprises a scanning optical system (5) for scanning in vivo tissue with a laser beam scanning spot and a light receiving optical system (6) for focusing on a light receiving plane thereof an image of the area in the vicinity of the scanning point at an image point conjugate with the scanning point. Photosensors (a, b, c, d) are disposed at prescribed positions in the light receiving plane for measuring light scattered from the tissue at prescribed positions in the vicinity of the image point conjugate with the scanning spot and the results of the measurement are analyzed to obtain information on blood flowing at a depth with the tissue. A dichromatic mirror or a half mirror (7) is disposed between the scanning and measurement systems for reflecting an image of the measurement region (P) to a TV camera (8). Information regarding the position of the scanning spot is superimposed on the video image from the TV camera so that the scanning spot can be positioned while it is being monitored on a display device (15).

Description: BACKGROUND OF THE INVENTION Field of the Invention This invention relates to an apparatus for measuring blood flow, and more particularly to an apparatus for noninvasively obtaining blood flow information within in vivo tissue. Description of the Prior Art Laser Doppler apparatuses or laser speckle apparatuses have been marketed as apparatuses for noninvasively obtaining information on blood flow. These measure blood flow factors by directing a laser beam into the blood stream, picking up light scattered by erythrocytes moving in the blood, and analyzing the frequency spectrum of the received light for determining the frequency gradient. An apparatus based on this method is disclosed, for example, in Japanese Patent Public Disclosure Sho 60(1985)-203235. Such conventional apparatuses use a laser beam projecting probe and a light receiving probe, both constituted of optical fibers, and the measurement depth within the in vivo tissue is regulated by adjusting the distance between the probes (See Fujii et al., Measurement of blood flow in skin using laser beam phenomenon (V) (Japan Laser Medical Magazine), Vol. 6, No. 3 (January 1986)). An example of the arrangement used is shown in Figure 4. A laser beam is directed into in vivo tissue P from an optical fiber F1 and the scattered light is received by an optical fiber F2. The intensity of the light received by the light receiving fiber is governed by its distance from the beam projecting fiber. Assuming the tissue to be a perfect light scattering body, Fujii et al. approximated the intensity of the light received by the light receiving fiber F2 as shown below (Fujii et al., Evaluation of skin blood flow using laser speckle phenomena (VII) (The Journal of Japan Society for Laser Medicine), Vol. 7, No. 3 (January 1987)). Im = I 0 Exp {- γ (r1 + r2)} where Im: intensity of received light I₀: intensity of irradiating beam γ: coefficient of attenuation owing to absorption and scattering r1: distance between end surface P1 of beam projecting fiber and light scattering particles (erythrocytes) r2: distance between end surface P2 of light receiving fiber and light scattering particles (erythrocytes) This equation being that of an ellipse having its foci at the points P1 and P2 where the light enters and leaves the tissue, it can be seen that the length of the light path for which scattered light can be received increases with increasing distance between the points P1 and P2. In other words, scattered light from deeper parts of the tissue can be received by increasing the distance between the optical fibers F1 and F2. As this conventional arrangement requires the optical fiber probes to be brought in contact with the tissue with respect to which measurement is being conducted, it is apt to have undesirable effects on the patient, such as making him or her feel uneasy or uncomfortable. Scanning of a large measurement region using the conventional arrangement involves the troublesome work of repeatedly repositioning of the measurement probes and, moreover, requires the position information to be recorded after each repositioning. The measurement work is thus complicated and laborious. SUMMARY OF THE INVENTION An object of the present invention is therefore to provide an apparatus capable of obtaining blood flow information from a depth within in vivo tissue in a contactless manner without using optical fibers or the like, of visually displaying the measurement region, and of enabling positional information relating to a large measurement region to be acquired simply and quickly during the measurement. In accordance with the present invention, there is provided an apparatus for measuring the blood flow comprising: a scanning optical system for scanning a measurement plane of an in vivo tissue in a desired pattern with a scanning spot formed by a coherent light beam; a light receiving optical system for focusing an image of the measurement plane on an image plane in the vicinity of a point conjugate with a scanning spot formed by the scanning optical system; at least one photodetecting means disposed at prescribed positions in the vicinity of the point conjugate with the scanning spot for measuring light scattered from the in vivo tissue to provide information on blood flowing at a depth within the in vivo tissue; video imaging means for receiving a visible image of the measurement plane and converting it into a video image; and image superimposing means for superposing information relating to the position of the scanning spot on the video image and displaying the result as a composite visible image; characterised in that the light receiving system shares at least a part of optical components of the scanning optical system; and the at least one photodetecting means is in the image plane and is disposed offset from the point conjugate with the scanning spot so that the depth of the measurement region is governed by the distance between the point conjugate with the scanning spot and the at least one photodetecting means. The apparatus for measuring blood flow according to the invention enables measurement of various data relating to blood flow at a depth within in vivo tissue to be carried out in a totally contactless manner, to be accomplished in respect of a large measurement region simply and at high speed while monitoring the measurement position on the visible image, and to be conducted without the need for mechanical positioning. In addition, it is structurally simple and inexpenvive to manufacture. BRIEF DESCRIPTION OF THE DRAWINGS The purposes and features of the present invention will become more apparent from a consideration of the following detailed description taken in conjunction with the accompanying drawings in which: Figure 1 is a perspective view of an apparatus for measuring blood flow in accordance with the present invention; Figure 2 is a schematic view for explaining the positional relationship between a scanning spot and photosensors within the light receiving plane (image plane) of the apparatus for measuring blood flow of Figure 1; Figure 3 is a plan view showing the positional relationship between an object and the light receiving plane (image plane); Figure 4 is a diagram for explaining the conventional measurement method; Figure 5 is flowchart of procedures for image superimposition; and Figures 6a and 6b are graphs showing the qualitative relationship between blood flow velocity and the speckle intensity power spectrum. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS The invention will now be described in detail on the basis of the preferred embodiment illustrated in the drawings. Figure 1 shows the basic arrangement of the optical system of an apparatus for measuring blood flow embodying the present invention. A laser beam emitted by a laser beam source 3 passes through the center hole of a perforated mirror 4 and the center of a lens 1, is reflected in turn by mirrors 5a, 5b of a galvanoscanner 5 disposed for conducting two-dimensional scanning, and thus scans a measurement region P. A laser beam source which emits a near infrared beam is used so as to minimize the amount of the laser beam light absorbed by the in vivo tissue. The measurement region P is further illuminated by white light from a source not shown in the figures. A dichroic mirror 7 disposed between the galvanoscanner 5 and the measurement region P transmits near infrared light and reflects light of other wavelengths toward a TV camera 8 so as to enable the TV camera 8 to pick up an image of the measurement region P. The TV camera 8 transmits the picked-up measurement region P image (of non-near infrared light reflected by the dichromatic mirror 7) to an image memory 14 for synthesizing the image (picture) from the TV camera 8 and an image obtained from a light receiving section 6 to be described later. Since the in vivo tissue constituting the measurement region P is as light scattering body, it emits scattered light. The scattered light from blood corpuscles within the tissue blood vessels is partially scattered and partially absorbed by the tissue. Light scattered by the tissue passes through the dichroic mirror 7 and the lens 1 and is reflected by the perforated mirror 4 through a lens 2 to form an image at a plane of the light receiving section 6. The perforated mirror 4 is disposed between the lenses 1 and 2 so as to prevent the laser beam from the laser beam source 3 from reaching the light receiving section 6. The image focusing system constituted by the lens 1, the lens 2 and the perforated mirror 4 is required to have a focal lenght that is large enough to avoid image blurring owing to oscillation of the mirrors 5a, 5b. For this purpose, therefore, the focal arrangement illustrated in Figure 3 is established as regards the light receiving system at the focal plane and at the object surface. (The galvanoscanner 5 is represented schematically in Figure 3.) An example of the arrangement of the light receiving section is shown in Figure 2. As shown in this figure, photosensors a - d are disposed at positions offset from the scanning spot. Differently from conventional apparatus for measuring blood flows based on laser speckle or laser Doppler principle, the apparatus for measuring blood flow according to this invention does not use optical fiber probes and, therefore, the depth of the measurement region is governed by the distance at the light receiving plane (image plane) between the scanning spot and the photosensors a - d, the numerical aperture of the lens 1 and the area of the sensors. Placing sensors at four locations as shown in Figure 2 makes it possible to receive information from a single scanning spot at four points and thus reduces the measurement time. The blood flow distribution can be measured at different depths by varying the distance between the scanning spot and the light receiving points and the so obtained information can be displayed on, for example, a display 15 in the manner described below. The video image (picture) output by the TV camera 8 and laser beam scanning position information obtained from the galvanoscanner 5 are synthesized in the image memory 14 in accordance with the procedures indicated in Figure 5 and the result is output to the display 15. The procedures of Figure 5 are executed by a control unit 16 (constituted as a computer or the like) for overall control of the apparatus for measuring blood flow. The procedure begins in step S1 in which the picture output by the TV camera 8 is read into the image memory 14. In the following step S2 the current laser beam scanning position is determined from position control information obtained from the galvanoscanner 5, whereafter a calculation is conducted in step S3 to determine what position within the picture output by the TV camera 8 the scanning position corresponds to. The procedure then moves to step S4 in which, based on the result of the calculation in step S3, information indicating the current scanning position (in the form of a dot or the like) is superimposed on the TV camera picture in the image memory 14 and the result is displayed on the display 15. If a plurality of light receiving elements (photosensors) are disposed at the light receiving section 6 in the aforesaid manner, the corresponding positions are also displayed. In the following step S5, blood flow data is measured in a manner to be explained later and, if desired, also superimposed on the TV camera picture appearing on the display 15. The procedure then moves through steps S6 to S8 for controlling the scanning position, and if there is a change in the scanning position the procedures of steps S1 to S5 are repeated. In such an arrangement, the beam (spot) of light output by the laser beam source 3 is deflected by galvanoscanner 5 so as to scan the measurement region P and scattered light from the measurement region P passes back through the lenses 1 and 2 of the scanning optical system to form an image of the area in the vicinity of the scanning spot on the light receiving section 6. The four photosensors a - d disposed on the light receiving section 6 at prescribed distances from the image of the scanning spot receive only that part of the scattered light reaching their respective positions. Using the variation in this scattered light is the main information regarding blood flow at the prescribed depth, it is then possible by analysis to determine the blood flow within the measurement region. If a beam including light of more than one wavelength is used, the differences among the scattered amounts of the different wavelength lights can be analyzed as spectral information for determining the oxygen saturation at prescribed points within a given plane. On the other hand, where a beam (spot) from a laser beam source is scanned in a prescibed manner and the dynamic spectral signals from the individual scanned points are analyzed, it becomes possible to determine the blood flow velocity distribution at a given depth within the in vivo tissue. As a method for analysing oxygen saturation and blood flow velocity are well known, only the basic principles will be discussed briefly here. The oxygen saturation is determined from the amount of light the blood absorbs. Lambert-Beer's law defines the absorbance A of a solution in terms of incident light I in and transmitted light I out as A = log (I in / I out ) = ECL where E is the absorbance coefficient at the wavelength of the light used, C is the substance concentration, I in is the amount of incident light, L is the length of the optical path and I out is the amount of transmitted light. In the case of blood, since the absorbance is almost totally accounted for by hemoglobin, C in the aforesaid equation can be considered to be the hemoglobin concentration. The coefficient of absorbance of hemoglobin varies with the saturation S and the wavelength as follows: E = Er - S (Er - Eo) where Er and Eo are the absorbance coefficients when S = 0 and S = 1, respectively. Where A₁ and A₂ are the absorbances at wavelengths λ1 and λ2 A 1 /CL 1 = E 1 = Er 1 - S (Er 1 -Eo 1 ) A 2 /CL 2 = E 2 = Er 2 - S (Er 2 -Eo 2 ) If the length of the optical path is the same for both wavelengths, L = L 1 = L 2 and, therefore, the absorbance ratio R for λ₁ and λ₂ can be expressed as R = (A 1 /A 2 ) = { E r1 - S(E r1 - E o1 )}/ {E r2 - S (E r2 - E o2 )} The oxygen saturation S can therefore be expressed as S ={E r1 - RE r2 }/ {(E r1 - E o1 ) - R(E r2 - E o2 )} whereby the oxygen saturation can be obtained from the ratio of the absorbances at two different wavelengths. The oxygen saturation can therefore be determined by irradiating the tissue with light of two different wavelengths in the aforesaid manner. Blood flow velocity is measured by utilizing the fact that, when erythrocytes are irradiated by a laser beam, the frequency at which the intensity of the light scattered thereby varies is a function of their velocity. The light scattered by erythrocytes moving within an in vivo blood vessel forms what is referred to as a "boiling speckle" pattern. It is known that when the intensity variation of such speckles is frequency analyzed with respect to a given light receiving region on the tissue surface, the velocity of the erythrocytes is found to be related to the distribution of the power spectrum as shown in Figures 6a and 6b. When the erythrocyte velocity is high, the spectral distribution extends to higher frequencies. Taking advantage of this fact, the blood flow velocity is determined from the gradient of the power spectrum. Nohira, Shintomi, Ohura, Fujii, Asakura et al. determined blood flow velocity by finding the ratio of the absolute values of 40 Hz and 640 Hz signals. (See, for example, Evaluation of skin blood flow using laser speckle phenomena (III) and (IV), The Journal of Japan Society for Laser Medicine, Vol. 5, No. 3.) In the present invention, since the galvanoscanner 5 is used both for scanning and as part of the light receiving system, the received light field is scanned simultaneously with the scanning spot. The embodiment of the invention described earlier, for example, is characterized in that the scanning spot and photosensors can, as a combined pair, be disposed for contactless scanning with the photosensors maintained in a fixed interval, whereby it becomes possible to position the measurement point while visually observing the measurement region on the display 15. With the beam projecting fiber and beam receiving fiber of the conventional apparatus for measuring blood flow referred to earlier, it is not possible to combine the measured results with measurement point position information, even by conducting measurement at a large number of points. In contrast, the apparatus for measuring blood flow according to the present invention is able to provide blood flow or oxygen saturation information including positional information. Differently from conventional apparatuses of this type, it thus enables measurement while carrying out completely contactless positional scanning. Moreover, once the object with respect to which measurement is to be conducted and the light receiving apparatus have been positioned, it becomes possible by laser beam scanning to carry out the measurement simply and quickly while visually observing a large measurement region. In the embodiment described in the foregoing the simultaneous measurement of scattered light data associated with a single scanning spot at four light receiving points (more if the number of the sensors is increased) enables the measurement to be conducted at high speed. In addition, since the scanning optical system and the light receiving optical system use some components in common, the apparatus becomes simpler in structure and, accordingly, less expensive to fabricate. While in the embodiment set out in the foregoing the light receiving section was explained has having four photosensors disposed around the scanning spot at the center, the number of photosensors and their locations can be changed variously in line with the desired measurement depth and the like. It is also possible to constitute the photosensors of the light receiving section as a photomultiplier tube equipped with a mask for defining a plurality of light receiving positions. With this arrangement, the number and positions of the photosensors can be easily varied by using different masks.

Claims: An apparatus for measuring the blood flow comprising: a scanning optical system (1,5) for scanning a measurement plane (P) of an in vivo tissue in a desired pattern with a scanning spot formed by a coherent light beam (3); a light receiving optical system (1,2,4,5,6) for focusing an image of the measurement plane on an image plane (6) in the vicinity of a point conjugate with a scanning spot formed by the scanning optical system; at least one photodetecting means (a,b,c,d) disposed at prescribed positions in the vicinity of the point conjugate with the scanning spot for measuring light scattered from the in vivo tissue to provide information on blood flowing at a depth within the in vivo tissue; video imaging means (8) for receiving a visible image of the measurement plane and converting it into a video image; and image superimposing means (14) for superposing information relating to the position of the scanning spot on the video image and displaying the result as a composite visible image; characterised in that the light receiving system shares at least a part of optical components (5) of the scanning optical system; and the at least one photodetecting means (a,b,c,d) is in the image plane (6) and is disposed offset from the point conjugate with the scanning spot so that the depth of the measurement region is governed by the distance between the point conjugate with the scanning spot and the at least one photodetecting means (a,b,c,d). An apparatus as claimed in claim 1, wherein the light receiving optical system (1,2,4,5,6) comprises a focusing lens (1), the numerical aperture of which is also a factor governing the measurement depth. An apparatus as set forth in claim 1 or 2, wherein the scanning optical system includes a galvanoscanner (5), which is shared by the light receiving optical system and produces the information relating to the position of the scanning spot. An apparatus as set forth in any preceding claim further comprising light splitting means (7) disposed between the scanning optical system and the tissue for transmitting the wavelength of the laser beam to the light receiving optical system and reflecting light of other wavelengths toward the video imaging means. An apparatus as set forth in any preceding claim, comprising means to display the position of the photodetecting means on the superimposed image. An apparatus as set forth in any preceding claim, further comprising means for calculating oxygen saturation of blood at a depth within the tissue on the basis of erythrocyte light absorbance determined by scanning a two-dimensional measurement plane of the tissue with the scanning spot and measuring the intensity of light scattered at prescribed positions in the vicinity of the image point conjugate with the scanning spot. An apparatus as set forth in any of claims 1 to 5, further comprising means for calculating two-dimensional erythrocyte flow velocity distribution at a given depth within the tissue by scanning a two-dimensional measurement plane of the tissue with the scanning spot, measuring variation in the intensity of light scattered at prescribed positions in the vicinity of the image point conjugate with the scanning spot, and analyzing the result of the measurement.

Inventors: ISHIKAWA MUNEHARU C O KOWA CO, TANIJI AYAFUMI C O KOWA CO, ISHIKAWA, MUNEHARU, C/O KOWA CO., TANIJI, AYAFUMI, C/O KOWA CO.
Applicants: KOWA CO, KOWA COMPANY LTD.
Application year: 1991
Main classification: A61B3
IPC codes: A61B5, A61B3