WO2014170985A1 - 流体濃度測定装置 - Google Patents
流体濃度測定装置 Download PDFInfo
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- WO2014170985A1 WO2014170985A1 PCT/JP2013/061486 JP2013061486W WO2014170985A1 WO 2014170985 A1 WO2014170985 A1 WO 2014170985A1 JP 2013061486 W JP2013061486 W JP 2013061486W WO 2014170985 A1 WO2014170985 A1 WO 2014170985A1
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- light
- optical path
- fluid
- light receiving
- tube
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/59—Transmissivity
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/01—Arrangements or apparatus for facilitating the optical investigation
- G01N21/03—Cuvette constructions
- G01N21/0303—Optical path conditioning in cuvettes, e.g. windows; adapted optical elements or systems; path modifying or adjustment
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/47—Scattering, i.e. diffuse reflection
- G01N21/49—Scattering, i.e. diffuse reflection within a body or fluid
- G01N21/53—Scattering, i.e. diffuse reflection within a body or fluid within a flowing fluid, e.g. smoke
- G01N21/532—Scattering, i.e. diffuse reflection within a body or fluid within a flowing fluid, e.g. smoke with measurement of scattering and transmission
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/47—Scattering, i.e. diffuse reflection
- G01N21/49—Scattering, i.e. diffuse reflection within a body or fluid
- G01N21/53—Scattering, i.e. diffuse reflection within a body or fluid within a flowing fluid, e.g. smoke
- G01N21/534—Scattering, i.e. diffuse reflection within a body or fluid within a flowing fluid, e.g. smoke by measuring transmission alone, i.e. determining opacity
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/84—Systems specially adapted for particular applications
- G01N21/85—Investigating moving fluids or granular solids
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
- G01N33/483—Physical analysis of biological material
- G01N33/487—Physical analysis of biological material of liquid biological material
- G01N33/49—Blood
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
- G01N33/483—Physical analysis of biological material
- G01N33/487—Physical analysis of biological material of liquid biological material
- G01N33/49—Blood
- G01N33/4915—Blood using flow cells
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/01—Arrangements or apparatus for facilitating the optical investigation
- G01N21/03—Cuvette constructions
- G01N2021/0364—Cuvette constructions flexible, compressible
Definitions
- the present invention relates to an apparatus for measuring the concentration of a fluid flowing in a light-transmitting and deformable pipe based on the Lambert-Beer law.
- the measuring method and measuring device measure the concentration of a processing liquid as a fluid for cleaning a semiconductor wafer
- a plurality of measuring bodies are provided in the middle of the processing liquid supply pipe, and a light transmitting part in which the optical path length of the light passing through the processing liquid is different is provided in each measuring body, and the optical path length corresponding to the properties of the processing liquid is provided.
- the light from the light source is supplied to the light transmission part, and the light transmitted through the processing liquid in the light transmission part is received by the photodetector and the intensity of the light is examined. From the intensity of the light, the Lambert-Beer law is used. Based on this, the concentration of the treatment liquid is obtained.
- the optical path length in each light transmitting portion is strictly determined, and therefore the fluid concentration can be easily obtained using a calculation formula in which the optical path length is set in advance. Can do.
- the conventional device is applied to measure the concentration of a fluid such as blood or a chemical solution flowing in a light-transmitting conduit such as a resin tube or a glass tube, light is transmitted to the optical path crossing the light-transmitting conduit.
- a light-transmitting conduit such as a resin tube or a glass tube
- the inner diameter may change due to the deformation. Therefore, it is very difficult to measure the concentration of blood, chemicals, etc. in such a case, and it has been practically impossible to measure the concentration.
- the present inventor traverses light from the same light source through a light-transmitting pipe at a plurality of places, and obtains the light intensity at each place, thereby calculating the pipe from the calculation based on the Lambert-Beer law.
- a fluid concentration measuring device that eliminates the influence of the inner diameter and wall thickness has been proposed (PCT / JP2013 / 54664 international application).
- the setting of the optical path in the tube wall is calculated at each light receiving point. It is set at a right angle to the tube wall, while the actual optical path crosses the tube wall diagonally, and the tilt angle varies depending on the difference in refractive index, further increasing the calculation accuracy. Has been found to have room for improvement.
- the present invention fixes the light receiving portion with respect to the light supply portion on the opposite side of the diameter direction of the pipe and maintains the optical path at right angles to the extending direction of the pipe.
- An object of the present invention is to advantageously solve the problem of a fluid concentration measuring device.
- the fluid concentration measuring device of the present invention is a device for measuring the concentration of a fluid flowing in a pipe having a light-transmissive and deformable tube wall.
- a light source that supplies light into the conduit from a light supply location on the surface of the conduit; At the light receiving point located on the opposite side of the diameter direction of the pipe with respect to the light supply point, the light that has been supplied and passed through the wall of the pipe and the fluid in the pipe is received.
- a light receiving element that outputs a signal indicating the intensity of the light
- Optical path distance setting means for setting a plurality of optical path distances between the light supply location and the light receiving location; Based on the Lambert-Beer law from the light intensity at each of the plurality of optical path distances, light from the light supply position is received at the light receiving position at each optical path distance.
- a fluid concentration output that obtains and outputs a plurality of relational expressions indicating the relationship between the intensity and the concentration of the fluid, and obtains and outputs the concentration of the fluid from the light intensity at the light receiving location based on the relational expressions at the plurality of optical path distances.
- Means, It is characterized by comprising.
- the light source is a surface of the pipe line.
- the light is supplied from the upper light supply point into the pipe, and the light receiving element is located at the opposite side of the diameter direction of the pipe with respect to the light supply point.
- the light passing through the inside of the pipe and the fluid in the pipe at a right angle to the extending direction of the pipe and outputting a signal indicating the intensity of the light, and the optical path distance setting means is configured to supply the light supply point.
- a plurality of optical path distances between the optical path and the light receiving location, and the fluid concentration output means determines each optical path based on the Lambert-Beer law from the light intensity at the light receiving location at each of the optical path distances.
- Light from the light supply point at a distance A plurality of relational expressions indicating the relationship between the light intensity and the fluid concentration when receiving light at the light receiving point are obtained, and the fluid is calculated from the light intensity at the light receiving point based on the relational expressions at the plurality of optical path distances. The concentration of is calculated and output.
- the fluid concentration measuring apparatus of the present invention light passing through an optical path obliquely crossing the pipe line with respect to the extending direction is not measured, and therefore, a transparent and deformable pipe wall such as a resin tube is provided. It is possible to measure the concentration of fluid such as blood and chemicals flowing through the pipe line with high accuracy.
- the optical path distance setting means has a plurality of pairs of the light supply location and the light receiving location, each having a different interval, and the light supply location and the light receiving location are The optical path distance may be changed by selectively using a pair, and in this way, a plurality of optical path distances can be set without changing the optical path distance, so that the measurement time can be shortened.
- the optical path distance setting means may change an optical path distance between the same light supply location and the light receiving location by changing an interval between them. In this way, since the optical path distance can be set arbitrarily, it is possible to easily cope with changes in the fluid concentration, and since the same light source and light receiving element are used, measurement due to differences in the light source and light receiving element is possible. The error can be eliminated.
- the optical path distance setting means has a plurality of pairs of the light supply location and the light receiving location, the intervals of which are different from each other.
- One of the pairs may be one that changes the optical path distance between them by changing the distance between the same light supply location and the light receiving location, and in this way, the pair that changes the optical path distance. Since the optical path distance can be set arbitrarily by using, it is possible to easily cope with changes in the fluid concentration, and once the relational expression is found, the measurement time can be shortened by using a pair of fixed optical path distances. Measurements can be performed continuously in real time.
- the fluid concentration output means indicates the relationship between the light intensity and the fluid concentration at the light receiving location at each of the plurality of optical path distances obtained and stored in advance.
- a table may be used to determine and output the fluid concentration from the light intensity at the light receiving location. By using such a table, the fluid concentration can be easily determined in a short time from the light intensity at the light receiving location. Can be output.
- (A)-(c) is explanatory drawing which shows typically the external appearance of three types of Examples of the fluid concentration measuring apparatus of this invention, respectively. It is a block diagram which shows collectively the electric constitution of the fluid concentration measuring apparatus of the said 3 types of Example. It is explanatory drawing which shows description of the code
- FIGS. 1 to 5 are explanatory views showing the measurement principle and calculation method of the fluid concentration in the three types of embodiments of the fluid concentration measuring device of the present invention.
- FIGS. 1 (a) to 1 (c) are explanatory views schematically showing the appearance of three types of embodiments of the fluid concentration measuring device of the present invention, respectively, and are shown in FIGS. 1 (a) to (c).
- Each of the three types of devices measures the concentration of blood as a fluid flowing in a substantially transparent resin tube as a conduit with a light transmissive and deformable tube wall.
- the fluid concentration measuring apparatus shown in FIG. 1 (a) is compressed in the diameter direction with a resin tube (not shown) passed through a groove 1a extending in the horizontal direction in the figure at the center of the case 1.
- Two pairs of light emitting / receiving units 4 which are pairs of the light emitting unit 2 and the light receiving unit 3 fixed so as to face the side wall of the groove 1a of the case 1 so as to be deformed, and as these light emitting / receiving unit pairs 4,
- the optical path distance between the light emitting unit 2 and the light receiving unit 3 is a predetermined short distance S
- the optical path distance between the right short distance unit pair 4S and the light emitting unit 2 and the light receiving unit 3 is a predetermined long distance L.
- two types of the long distance unit pair 4L on the left side are set. Therefore, the two pairs of light emitting / receiving units 4 function as optical path distance setting means.
- the two pairs of light emitting / receiving units 4 need not be adjacent to each other, and are preferably separated from each other to such an extent that the measurement is hardly affected.
- the measurement with one light emitting / receiving unit pair 4 is not performed while the measurement with one light emitting / receiving unit pair 4 is performed. good.
- the fluid concentration measuring apparatus shown in FIG. 1 (b) is compressed and deformed in the diametrical direction with a resin tube (not shown) passed through a groove 1a extending in the horizontal direction in the figure at the center of the case 1.
- the light-emitting unit 2 and the light-receiving unit 3 are arranged so as to face both side walls of the groove 1a of the case 1 and supported by the case 1 so as to be movable toward and away from each other as indicated by arrows in the figure.
- a pair of light emitting / receiving unit 4M, and the light emitting unit 2 and light receiving unit 3 of the light emitting / receiving unit pair 4M are moved relative to each other in the approaching and separating directions, that is, in the diameter direction of the resin tube.
- An optical path distance changing mechanism (not shown) for changing the optical path distance between the light emitting unit 2 and the light receiving unit 3 is provided. Therefore, this optical path distance changing mechanism functions as an optical path distance setting means.
- the fluid concentration measuring device shown in FIG. 1 (c) is a combination of the half of the device shown in FIG. 1 (a) and the device shown in FIG. 1 (b).
- the light emitting unit 2 and the light receiving unit fixed to face the side wall of the groove 1a of the case 1 so as to be compressed and deformed in the diametrical direction with a resin tube (not shown) passed through the groove 1a extending in the direction interposed therebetween
- a pair of short-distance unit 4S or long-distance unit pair 4L is provided as a pair of light emitting / receiving units 4 that is paired with 3 and a groove 1a of case 1 so as to be compressed and deformed in the diametrical direction with the resin tube interposed therebetween.
- the light emitting / receiving unit is a pair of light emitting unit 2 and light receiving unit 3 which are arranged facing each other and supported by case 1 so as to be movable toward and away from each other as indicated by arrows in the figure.
- a pair 4M is provided, and the light emitting unit 2 and the light receiving unit 3 of the light emitting / receiving unit pair 4M are moved relative to each other in the approaching and separating directions, that is, in the diameter direction of the resin tube.
- an optical path distance changing mechanism (not shown) for changing the optical path distance between the two. Therefore, the optical path distance changing mechanism and the light emitting / receiving unit pair 4 having a fixed distance function as optical path distance setting means.
- the light emitting unit 2 incorporates a light emitting element that emits light when supplied with electricity, such as a light emitting diode (LED) or a laser diode as a light source, and positions the light from the light emitting element on the surface of the resin tube.
- the resin is supplied into the resin tube from the light supply location.
- the light receiving unit 3 includes a light receiving element that receives light and generates electricity, such as a photodiode or a phototransistor, and receives light supplied from the light emitting unit 2 and transmitted through the resin tube. An electrical signal corresponding to the light intensity is output.
- the light emitting unit 2 and the light receiving unit 3 emit and receive light having a wavelength of about 590 nm as light having substantially the same extinction coefficient for both oxygenated hemoglobin of arterial blood and deoxygenated hemoglobin of venous blood.
- FIG. 2 is a block diagram collectively showing the electrical configuration of the fluid concentration measuring apparatus of the above three types.
- the first unit pair 4 shown in FIG. One of the second unit pair 4 is a short-distance unit pair 4S and the other is a long-distance unit pair 4L. Since the optical path distance of these unit pairs 4 is fixed, a motor driver 16 and a motor 17 described later The optical path distance changing mechanism 18 is not provided.
- light emitted from the light emitting elements in the two light emitting units 2 respectively driven by the light emitting element driver 11 is emitted from the light emitting unit 2 and the light receiving unit 3 of the two pairs of units 4.
- the tube wall near the light emitting unit 2 of one resin tube TB that is sandwiched between and compressed in the diametrical direction, the blood BD that flows inside the resin tube TB, and the side far from the light emitting unit 2 (Opposite side), that is, the light passing through the tube wall close to the light receiving unit 3, is received by the light receiving elements in the two light receiving units 3 through the optical paths having different fixed distances, and received in the two light receiving units 3.
- Each element outputs an electric signal having a level corresponding to the intensity of received light.
- the output signals of the light receiving elements in the two light receiving units 3 are each amplified by an amplifier 12, high frequency noise components are removed by a low pass filter 13, and an analog signal is converted into a digital signal by an analog / digital converter (A / D) 14. It is converted and input to the central processing unit (CPU) 15.
- the CPU 15 controls the operation of the light emitting element driver 11 to selectively cause the light emitting units 2 of the two pairs of units 4 to emit light and avoid mutual interference, and the light receiving elements at the respective optical path distances.
- the concentration of blood BD in the resin tube TB is obtained from the output signal, and a signal indicating the concentration data is output. Therefore, the CPU 15 functions as fluid concentration output means.
- the first unit pair 4 shown in FIG. 2 is arranged facing the side wall of the groove 1a of the case 1 so as to be movable toward and away from each other.
- the light emitting / receiving unit pair 4M is a pair of the light emitting unit 2 and the light receiving unit 3 that are supported, and the second unit pair 4 is not provided, so that the light receiving element of the light receiving unit 3 of the second unit pair 4 2 is not provided for the first unit pair 4 and the motor driver 16, the motor 17, and the optical path distance shown in FIG. 2 are used instead of the amplifier 12, the low-pass filter 13, and the A / D 14.
- a change mechanism 18 is used instead of the amplifier 12, the low-pass filter 13, and the A / D 14.
- the CPU 15 functioning as a fluid concentration output means also sends a control signal to the motor driver 16, the motor driver 16 sends a drive current to the motor 17 according to the control signal, and the motor 17 changes the optical path distance according to the drive current.
- the mechanism 18 is operated, and the optical path distance changing mechanism 18 changes the optical path distance between the light emitting unit 2 and the light receiving unit 3 of the first unit pair 4 between a predetermined long distance L and a predetermined short distance S. As described above, the light emitting unit 2 and the light receiving unit 3 are moved in the approaching and separating directions.
- a cam is used to move at least one of the light emitting unit 2 and the light receiving unit 3, preferably both simultaneously in the approaching and separating directions with respect to the other, using a cam,
- the light-emitting unit 2 and the light-receiving unit 3 each having a female screw to be engaged with the male screw are moved simultaneously in the approaching and separating directions with respect to the other by rotating a drive shaft having both male and left-handed male screws.
- Any mechanism such as a screw mechanism can be used.
- the first unit pair 4 shown in FIG. 2 is arranged facing the side wall of the groove 1a of the case 1 so as to be movable toward and away from each other.
- a light emitting / receiving unit pair 4M which is a pair of the light emitting unit 2 and the light receiving unit 3 supported, and the second unit pair 4 shown in FIG. 2 is a short-distance unit pair 4S or a long-distance unit each having a fixed optical path distance. Pair 4L.
- FIG. 3 is a diagram for explaining the reference numerals in the embodiments described above.
- the absorption coefficient of the tube wall near the light receiving unit 3 of the resin tube is A ⁇ C1
- the absorption coefficient of the tube wall near the light receiving unit 3 of the resin tube is A ⁇ C2
- the absorption coefficient of blood in the resin tube is ⁇ H
- the concentration of C H when the optical path length is long distance L, and incident light intensity from the light-emitting unit 2 to the side of the tube wall close to the light-emitting unit 2 of the resin tube AIi, Idemitsu intensity from the tube wall AI L1, the light exit intensity from the blood AI L2, Idemitsu strength AI LO from the side of the tube wall close to the light receiving unit 3 of the resin tube into the light receiving unit 3, the gain of the amplifier a connected to the light receiving unit 3 G a, the When the output of the amplifier A is RAI LO and the optical path distance is the short distance S, the tube closer to the light emitting unit 2 of the resin tube from the light emitting unit 2 is selected.
- the incident light intensity on the wall is AIi
- the emitted light intensity from the tube wall is AI S1
- the emitted light intensity from the blood is AI S2
- the emitted light intensity from the tube wall of the resin tube closer to the light receiving unit 3 to the light receiving unit 3 the AI SO, the gain of the amplifier a connected to the light receiving unit 3 G a, the output of the amplifier a and RAI SO.
- these codes are, for example, light incident intensities AIi and BIi
- a and B are distinguished from two sensors (if there are two optical path length fixed sensors, they are distinguished, in the case of an optical path length variable sensor and an optical path length fixed sensor, they are I indicates the light intensity, and i indicates the input.
- Idemitsu strength AI LO, BI SO of A, B represents a distinction between two sensors, I is shows the light intensity, L is far, S is shown a short distance, O denotes an output.
- a and B in the light intensity AI L1 and BI S2 indicate the distinction between the two sensors, I indicates the light intensity, L indicates a long distance, S indicates a short distance, and 1 and 2 are positions where the light intensity is obtained. Indicates.
- a and B of the tube wall extinction coefficients A ⁇ C1 and B ⁇ C2 indicate the distinction between the two sensors, ⁇ indicates the extinction coefficient, C1 is the tube wall on the side close to the light emitting unit 2, and C2 is close to the light receiving unit 3.
- the side tube wall is shown.
- the tube wall thicknesses Al C1 and Bl C2 A and B indicate the distinction between the two sensors, l indicates the tube wall thickness, C1 indicates the tube wall closer to the light emitting unit 2, and C2 indicates the light receiving unit 3.
- G of the gains G A and G B indicates the amplification factor including the sensitivity of the light receiving element
- a and B indicate the distinction between the two sensors
- R of the amplifier outputs RAI SO and RBI SO indicates an actual measurement value. .
- FIG. 4 shows the operating principle of the fluid concentration measuring apparatus of the embodiment shown in FIG. 1A.
- the apparatus of this embodiment there are two types of optical paths: a fixed optical path length L and a fixed optical path length S.
- L the tube wall thickness, tube wall composition, incident light intensity, and amplifier amplification factor on these two types of optical paths may all be different.
- the tube wall extinction coefficients A ⁇ C1 , A ⁇ C2 , B ⁇ C1 and B ⁇ C2 are equal to each other, and the tube wall thicknesses Al C1 , Al C2 , and Bl C1 , Bl C2 are also equal to each other, It can be.
- DL can be set to 0.5 mm, for example.
- K in the expression the input light intensity difference, amplification index difference, since it is a value that includes all the tube wall thickness difference and the tube wall composition difference, once separately determined the precise value of the blood concentration C H from the outside It is shown that the measurement output of this apparatus can be corrected to a correct value if K is calculated by inserting.
- FIG. 5 shows the operation principle of the fluid concentration measuring apparatus of the embodiment shown in FIG. 1B.
- the apparatus of this embodiment there is one optical path having a variable optical path length, and two optical paths are provided on this optical path. Since the optical path lengths L and S are mechanically generated by the optical path distance changing mechanism 18, the tube wall thickness, the tube wall composition, the incident light intensity, the amplifier amplification factor are exactly the same, and only two optical path lengths are different. Can measure the data. Therefore, highly accurate concentration measurement values can be obtained without maintenance between measurements.
- the blood concentration C H of the resin tube Is required.
- the blood concentration C H is obtained from the amplifier outputs RAI LO and RAI SO obtained by switching between the optical path distance L and the optical path distance S, and the input light intensity difference and the tube wall composition difference are obtained. It shows that it is not affected. However, it is necessary to switch the optical path length for each measurement.
- FIG. 3 shows the principle of operation of the fluid concentration measuring device of the embodiment shown in FIG. 1 (c) as described above.
- the device of this embodiment has an optical path in the resin tube shown on the left side in FIG.
- the first unit pair 4M optical path length variable sensor (A)) having a pair of variable optical path lengths for setting the optical paths of the distances L and S and the optical path distance L or S in the resin tube shown on the right side in FIG.
- a second unit pair 4L or 4S optical path length fixed sensor (B)) having a pair of fixed optical path lengths for setting an optical path, and further between the light emitting unit 2 and the light receiving unit 3 of the first unit pair 4M.
- the motor driver 16, the motor 17, and the optical path distance changing mechanism 18 are provided as in the apparatus of the embodiment shown in FIG. Yes.
- step S1 the optical path of the optical path distances L and S is set by the first unit pair 4M having a variable optical path length, and the tube in the resin tube
- step S2 the optical path of the first unit pair 4M
- the optical path length of the first unit pair 4M is fixed to the long distance L and shown in FIG.
- the configuration is the same as that of the apparatus, and the subsequent measurement is performed using the correction data obtained previously. According to the apparatus of the embodiment shown in FIG. 1C, it is not necessary to switch between two types of optical path lengths for each measurement, and correction data can be obtained inside the apparatus. Can be done continuously.
- step S1 since the configuration is the same as that of the apparatus of the embodiment shown in FIG. 1B, the blood concentration is calculated by the equation (22) from the measured values at the two types of optical path lengths of the first unit pair 4M. C H is obtained.
- step S2 since the configuration in step S2 is the same as that of the apparatus of the embodiment shown in FIG. 1A, for example, the measured value of the first unit pair 4M with the optical path length L and the second unit pair with the optical path length S are used. From the measured value of 4S, the blood concentration CH is obtained by the equation (11).
- FIG. 6 is an explanatory view showing a more specific configuration example of the fluid concentration measuring device of the embodiment of FIG. 1B with the lid closed
- FIG. 7 shows the fluid concentration measuring device of the configuration example.
- the apparatus of this structural example can open and close the lid
- a light emitting unit 2 and a light receiving unit 3 which are provided with a case 1 having a 1a and which are arranged facing both side walls of the groove 1a of the case 1 and supported by the case 1 so as to be movable toward and away from each other.
- a pair of light emitting / receiving units 4M (only the light receiving unit 3 is shown in FIGS. 6 and 7).
- FIG. 8 is an explanatory view showing a pair of the light emitting unit 2 and the light receiving unit 3 inside the fluid concentration measuring device of the configuration example
- FIG. 9 is a diagram showing the light emitting unit 2 and the light receiving inside the fluid concentration measuring device of the configuration example. It is explanatory drawing which cuts off and partially shows the guide mechanism which guides relative movement with the unit 3, and the deck part of case 1 which covers the pair of the light emission unit 2 and the light reception unit 3, and forms the groove
- a cam plate 23 is disposed below the base plate 21 so as to be slidable in the extending direction of the groove 1a perpendicular to the extending direction of the guide rod 22 along the lower surface of the base plate 21.
- FIG. 10 is an explanatory view showing a motor-driven crank mechanism for changing the relative distance between the light emitting unit and the light receiving unit in the fluid concentration measuring device of the above configuration example
- FIG. 11 is a fluid concentration measuring device of the configuration example
- FIG. 12 is an explanatory diagram showing the configuration of the cam plate of the fluid concentration measuring device of the configuration example.
- the base of the crank arm 24 is fixed to the output shaft of the motor 17 composed of a servo motor with a speed reducer housed and fixed inside the case 1.
- the front end is connected to one end of the cam plate 23 via a link member 25 to constitute a crank mechanism for moving the cam plate 23 forward and backward in the extending direction of the groove 1a of the case 1. ing.
- FIG. 12 is an explanatory view showing the configuration of a cam plate for changing the relative distance between the light emitting unit and the light receiving unit in the fluid concentration measuring device of the above configuration example.
- the cam plate 23 here is a diagram of the cam plate 23. In the figure, it has two pairs of cam surfaces 23a and 23b that make a pair facing each other in the vicinity of the upper and lower sides, and a guide hole 23c that extends in the left-right direction in the center of the cam plate 23, the distance between the cam surface 23a which forms one of the pair is slightly wider than the distance between the cam surface 23b forming the other pair, the difference between these distances, the tube distance between the walls AL L farther It corresponds to a difference DL between the tube walls distance AL S closer.
- the cam surfaces 23a and 23b near the side portions of the cam plate 23 are smoothly connected to each other by curved surfaces.
- the two cam surfaces 23a and 23b project to the lower ends of the light emitting unit 2 and the light receiving unit 3, respectively.
- the projecting curved surfaces of the provided cam follower portions 2a and 3a face each other and are in sliding contact with the cam surfaces 23a and 23b.
- a compression spring (not shown) is interposed between the light emitting unit 2 and the light receiving unit 3, and this compression spring constantly urges the light emitting unit 2 and the light receiving unit 3 in the direction away from each other, and the cam follower.
- the slidable contact between the projecting curved surfaces of the portions 2a and 3a and the cam surfaces 23a and 23b is maintained, and a cam mechanism is constituted by these.
- a protrusion 21a protruding from the lower surface of the base plate 21 is slidably fitted into the guide hole 23c at the center of the cam plate 23, and thereby the groove 1a of the case 1 extends in the extending direction.
- a guide mechanism that guides the movement of the cam plate 23 is configured.
- the link member 25 causes the cam plate 23 to extend in the extending direction of the groove 1a of the case 1 and the light emitting unit. 2 and the light receiving unit 3 are moved forward and backward to the position where the projecting curved surfaces of the cam follower portions 2a and 3a projecting from the lower end portions of the light receiving unit 3 and the cam surface 23b contact the cam surface 23b. Is set to a predetermined distance on the far side or a predetermined distance on the near side. Therefore, according to this configuration example, the mechanism portion of the fluid concentration measuring apparatus of the embodiment shown in FIG. 1B can be configured, and highly accurate blood concentration measurement can be performed.
- the present invention has been described based on the illustrated examples, the present invention is not limited to the above-described examples and can be appropriately changed within the scope of the claims.
- the CPU 15 The blood concentration is obtained by performing arithmetic processing based on the light intensity in the light receiving unit 3 and is output, but instead of this, at the light receiving points at each of the plurality of optical path distances obtained and stored in advance. Using a table indicating the relationship between the light intensity and the fluid concentration, the fluid concentration may be obtained and output from the light intensity at the light receiving location.
- light having a wavelength of about 590 nm is used as light having substantially the same extinction rate for both oxygenated hemoglobin of arterial blood and deoxygenated hemoglobin of venous blood.
- light having a wavelength near 520 nm, 550 nm, 570 nm, or 805 nm may be used.
- the concentration of blood as a liquid is measured.
- it can also be used for measuring the concentration of other liquids, in which case the liquid is used as light supplied from the light source. It is preferable to select light having a wavelength with a high absorptance due to the difference in light intensity at the light receiving location depending on the thickness of the tube wall.
- light is supplied at a light supply location at two types of optical path distances, and the light is received at a light reception location to obtain the light intensity.
- the light intensity may be obtained at each light receiving location by setting the optical path distance, and in this way, the measurement accuracy can be further improved by averaging the obtained results.
- the fluid concentration measuring apparatus method of the present invention light passing through the optical path obliquely crossing the pipe line with respect to its extending direction is not measured, so that the light-transmitting and deformable pipe wall such as a resin tube is provided. It is possible to measure the concentration of fluid such as blood and chemicals flowing through the pipe line with high accuracy.
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Abstract
Description
前記管路の表面上の光供給箇所から前記管路内に光を供給する光源と、
前記光供給箇所に対しその管路の直径方向の反対側に位置する受光箇所で、前記供給されてその管路の壁内およびその管路内の流体内を通過して来た光を受光してその光の強度を示す信号を出力する受光素子と、
前記光供給個所と前記受光箇所との間の光路距離を複数設定する光路距離設定手段と、
それら複数の光路距離のそれぞれにおける前記受光箇所での光の強度からランベルト-ベールの法則に基づき、前記各光路距離をおいて前記光供給箇所からの光を前記受光箇所で受光する場合の光の強度と流体の濃度との関係を示す複数の関係式を求め、それら複数の光路距離での関係式に基づいて、前記受光箇所での光の強度から流体の濃度を求めて出力する流体濃度出力手段と、
を具えることを特徴とするものである。
先ず固定光路長LのセンサAについて考えると、ランベルトベールの式より、
また、この実施例の装置では、DLは例えば0.5mmに設定することができる。
(11)式におけるKは、入力光強度差、増幅率差、チューブ壁厚差およびチューブ壁組成差の全てを含む値であることから、一旦外部から別途求めた正確な血液濃度CHの値を入れてKを算出すればこの装置の測定出力を正しい値に補正できることを示している。
この(22)式は、光路距離Lと光路距離Sとを切り替えて測定することで得られるアンプ出力RAILO,RAISOから血液濃度CHが得られ、入力光強度差やチューブ壁組成差の影響を受けないことを示している。但し、測定の度ごとに光路長の切替えを行う必要がある。
1a 溝
1b 蓋
2 発光ユニット
2a,3a カムフォロワ部
3 受光ユニット
4 発光受光ユニット対
4L 遠距離発光受光ユニット対
4M 光路長可変発光受光ユニット対
4S 近距離発光受光ユニット対
11 発光素子ドライバー
12 アンプ
13 ローパスフィルタ
14 アナログ-デジタルコンバータ
15 CPU
16 モータードライバー
17 モーター
18 光路距離変更機構
21 ベース板
21a 突条
22 ガイドロッド
23 カム板
23a,23b カム面
23c ガイド孔
24 クランクアーム
25 リンク部材
26 光路距離変更機構
TB 樹脂チューブ
BD 血液
Claims (4)
- 光透過性でかつ変形可能な管壁を持つ管路内を流れる流体の濃度を測定する装置において、
前記管路の表面上の供光箇所から前記管路内に光を供給する光源と、
前記光供給箇所に対しその管路の直径方向の反対側に位置する受光箇所で、前記供給されてその管路の壁内およびその管路内の流体内を通過して来た光を受光してその光の強度を示す信号を出力する受光素子と、
前記光供給個所と前記受光箇所との間の光路距離を複数設定する光路距離設定手段と、
それら複数の光路距離のそれぞれにおける前記受光箇所での光の強度からランベルト-ベールの法則に基づき、前記各光路距離をおいて前記光供給箇所からの光を前記受光箇所で受光する場合の光の強度と流体の濃度との関係を示す複数の関係式を求め、それら複数の光路距離での関係式に基づいて、前記受光箇所での光の強度から流体の濃度を求めて出力する流体濃度出力手段と、
を具えることを特徴とする流体濃度測定装置。 - 前記光路距離設定手段は、間隔が互いに異なる前記光供給個所と前記受光箇所との対を複数対有し、それらの光供給個所と受光箇所との対を選択的に用いることで光路距離を変更するものであることを特徴とする、請求項1記載の流体濃度測定装置。
- 前記光路距離設定手段は、同じ前記光供給個所と前記受光箇所との間隔を変化させてそれらの間の光路距離を変更するものであることを特徴とする、請求項1または2記載の流体濃度測定装置。
- 前記流体濃度出力手段は、あらかじめ求めて記憶した、前記複数の光路距離のそれぞれにおける受光箇所での光の強度と流体の濃度との関係を示すテーブルを用いて、前記受光箇所での光の強度から流体の濃度を求めて出力するものである、請求項1から3までの何れか1項記載の流体濃度測定装置。
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PCT/JP2013/061486 WO2014170985A1 (ja) | 2013-04-18 | 2013-04-18 | 流体濃度測定装置 |
JP2015512246A JP6246793B2 (ja) | 2013-04-18 | 2013-04-18 | 流体濃度測定装置 |
US14/785,200 US9562858B2 (en) | 2013-04-18 | 2013-04-18 | Fluid concentration measuring device |
CN201380075615.4A CN105229448B (zh) | 2013-04-18 | 2013-04-18 | 流体浓度测定装置 |
EP13882184.8A EP2988113A4 (en) | 2013-04-18 | 2013-04-18 | DEVICE FOR MEASURING FLUID CONCENTRATION |
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EP (1) | EP2988113A4 (ja) |
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CN107533004A (zh) * | 2015-05-29 | 2018-01-02 | 尼普洛株式会社 | 透射光强度测定单元 |
WO2019013086A1 (ja) * | 2017-07-12 | 2019-01-17 | アルプス電気株式会社 | 分析装置および流路プレート |
WO2019098207A1 (ja) * | 2017-11-14 | 2019-05-23 | ジーニアルライト株式会社 | 体液分析装置 |
US11499961B2 (en) | 2017-11-14 | 2022-11-15 | Genial Light Co., Ltd. | Body fluid optical analysis device |
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US9308306B2 (en) * | 2014-02-24 | 2016-04-12 | Fresenius Medical Care Holdings, Inc. | Self calibrating blood chamber |
US9759651B2 (en) * | 2014-12-23 | 2017-09-12 | Magellan Diagnostics, Inc. | Combination optical hemoglobin and electrochemical lead assay |
CN106404721B (zh) * | 2016-08-25 | 2019-05-03 | 吴小戈 | 一种血液浓度检测装置 |
EP3660572A4 (en) * | 2017-07-26 | 2021-06-23 | Hamamatsu Photonics K.K. | SAMPLE MONITORING DEVICE AND SAMPLE MONITORING METHOD |
WO2022182913A1 (en) * | 2021-02-26 | 2022-09-01 | Vivonics, Inc. | Sensor apparatus for sensing characteristic of fluid, and method |
US20220334049A1 (en) * | 2021-04-15 | 2022-10-20 | Fenwal, Inc. | Adjustment Of The Thickness Of A Biological Fluid Being Monitored By An Optical Detection Assembly |
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EP2988113A4 (en) | 2016-12-21 |
JPWO2014170985A1 (ja) | 2017-02-16 |
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CN105229448A (zh) | 2016-01-06 |
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US9562858B2 (en) | 2017-02-07 |
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