Liver function testing apparatus

Abstract: In a liver function testing apparatus, light sources (11, 12) expose vital tissue (15) to first light of a wavelength absorbed by a specific dye dosed into blood of the vital tissue to be taken in and removed by the liver and second light of a wavelength not absorbed by the specific dye. Optical pulses obtained from the vital tissue are received by a light receiving element (13), the receiving output of which is sampled by an A-D converter (30) to be converted into digital signals. On the basis of variable components in the blood, a CPU (34) decides a coefficient of a regression line expression between first and second photoelectric conversion signals, to perform biocalibration. A value correlated with specific dye concentration in the blood is operated on the basis of sampling signals during a prescribed period after injection of the specific dye and the decided coefficient of the regression line expression, so that a coefficient of a simulation function as a function of time is obtained by using the method of least squares and an index R MAX expressing the total amount of hepatic cell function is obtained on the basis of the obtained coefficient.

Description: BACKGROUND OF THE INVENTION Field of the Invention The present invention relates to a liver function testing apparatus, and more specifically, it relates to a liver function testing apparatus for automatically performing measurement for testing/diagnosing liver function by injecting a specific color dye, which is selectively taken in and removed by the liver, into blood and measuring an index R MAX expressing the total amount of hepatic cell function. Description of the Prior Art An index R MAX expressing the total amount of hepatic cell function is highly evaluated and applied to judgement of adaptation to an operation in the domain of liver surgery, while being adapted to comprehend a case of a hepatic disease as well as to judge convalescence in the domain of medicine. In a conventional method of measuring such an index R MAX , blood for a blank test is collected from a testee in a tasting state. Then indocyanine green (hereinafter referred to as ICG) of 0.5 mg/kg is injected into the one antecubital vein within 30 seconds, to collect blood of 3 to 4 ml from the other antecubital vein after lapses of five, ten and 15 minutes from starting of injection of the ICG solution. Then, 1 ml of the obtained blood is diluted in a physiological salt solution of 2 ml, and colorimetry is performed through a spectrophotometer with a blank of blood serum for the blank test at a wavelength of 805 nm. Reading (OD) in such colorimetry is plotted on semilogarithmic paper, whereby ICG concentration from five to 15 minutes is linearly decreased. Zero-order concentration in blood is obtained from an intersection of a straight line connecting three points and the Y-axis. If a half value period (t 1/2 ) of specific dye concentration in blood is thereby obtained, a blood plasma disappearance rate K can be calculated from the following expression: K = 0.693/t 1/2 In the aforementioned three-point analysis method, ICG injection must be performed three times while changing dose quantities. In this case, doses of ICG are considered in various ways. For example, a testee may be dosed with 0.5 mg/kg, 1.0 mg/kg and 5.0 mg/kg of ICG on different days, or measurement may be made with doses of 0.5 mg/kg, 1.0 mg/kg and 2.0 mg/kg. Or, ICG may be injected three times with doses of 0.5 mg/kg, 3.0 mg/kg and 5.0 mg/kg or twice with doses of 0.5 mg/kg and 5.0 mg/kg on different days. Further, the index R MAX may be measured in one day with doses of 0.5 mg/kg, 1.0 mg/kg and 5.0 mg/kg, or ICG may be injected three times on different days with doses of 0.5 mg/kg, 1.0 mg/kg and 2.0 mg/kg. Blood collection and measurement of ICG concentration are performed similarly to the case of a dose of 0.5 mg/kg, to calculate the blood plasma disappearance rate K. The blood serum is previously diluted to six to 10 times since ICG concentration in blood is extremely high. A method of calculating the index R MAX is now described. Values of the blood plasma disappearance rate K with dose quantities of 0.5 mg/kg, 3.0 mg/kg and 5.0 mg/kg, for example, are 0.0568, 0.0376 and 0.0334 respectively. A liver removal ratio R is calculated from K (min.) x D (mg/kg), and hence: R = 0.0568 x 0.5 = 0.0284 when the dose quantity is 0.5 mg/kg, R = 0.0376 x 3.0 = 0.1128 when the dose quantity is 3.0 mg/kg, and R = 0.0334 x 5.0 = 0.1671 when the dose quantity is 5.0 mg/kg. Then, the values are plotted as shown in Fig. 21, with the X-axis representing the inverse numbers (1/D:(mg/kg)⁻¹) of the dose quantities and the Y-axis representing the inverse numbers (1/R:(mg/kg/min)⁻¹ of the removal ratios. The dose of 0.5 mg/kg is plotted as 2.00 on the X-axis and 35.21 on the Y-axis and the doses of 3.0 mg/kg is plotted as 0.33 on the X-axis and 8.86 on the Y-axis, while the doses of 5.0 mg/kg is plotted as 0.20 on the Y-axis and 6.00 on the Y-axis. A regression line of these three points is obtained as follows: Y = a + bX = 3.1658 + 16.0366X (r = 0.999) The intersection of the line and the Y-axis shows 1/R MAX and hence the index R MAX is represented by the inverse number of a , as 1/a = 0.32 mg/kg/min. In accordance with a two-point analysis method of 0.5 mg/kg and 5.0 mg/kg, the index R MAX is calculated from a regression line Y = 2.7544 + 16.2278X of Lineweaver-Burk plotting as 0.35 mg/kg/min. In the aforementioned method of measuring the index R MAX , however, some conditions are required in theory adaptation, while errors may be caused from various sources in the process of measurement and calculation. For example, impossible minus measurement values are recognized once in a while. Further, when the dose quantity is changed three times for measuring the index R MAX as hereinabove described, intravenous injection must be made 15 times ( blood collection by four times + ICG injection) x 3 ) to extremely increase burdens on the patient, while several days are required for pretesting. EP 0 298 122 discloses a liver function inspection apparatus which is capable for obtaining blood parameters by an optical measurement with 2 different wave lengthes. This document represents state of the art according to article 54(3) and (4) EPC. SUMMARY OF THE INVENTION Accordingly, a principal object of the present invention is to provide a liver function testing apparatus which can reduce mental and physical burdens on a testee, to automatically measure an index expressing the total amount of hepatic cell function. Another object of the present invention is to provide a liver function testing apparatus which can extremely simply and automatically measure an index expressing the total amount of hepatic cell function by injecting ICG only once. Still another object of the present invention is to provide a liver function testing apparatus which can automatically select a prescribed light source in response to the dose quantity of a specific dye to measure an index expressing the total amount of hepatic cell function. A further object of the present invention is to provide a liver function testing apparatus which can remove artifacts such as blood flow disturbance, vibration of an organism and pulsation in the organism in attachment of a sensor to the organism by performing biocalibration in advance to measurement. Briefly stated, vital tissue is exposed to first light of a wavelength absorbed by a specific dye dosed into the blood of the vital tissue to be taken in and removed by the liver and second light of a wavelength not absorbed by the specific dye and first and second photoelectric conversion signals corresponding to the first light and the second light obtained from the vital tissue are sampled so that a coefficient of a regression line expression between the first and second photoelectric conversion signals is decided on the basis of variable components in the blood included in the sampled first and second photoelectric conversion signals to perform biocalibration. A value correlated with specific dye concentration in blood is operated on the basis of a sampling signal in a prescribed period after injection of the specific dye and the decided coefficient of the regression line expression to obtain a coefficient of a simulation function as a function of time on the basis of the operated value through the method of least squares, thereby to obtain an index R MAX expressing the total amount of hepatic cell function. Thus, according to the present invention, the index R MAX expressing the total amount of hepatic cell function can be measured by giving ICG injection only once with no blood collection dissimilarly to the conventional case, whereby mental and physical burdens on a testee can be extremely reduced. Further, artifacts such as blood flow disturbance, vibration of an organism, pulsation in the organism and change of the blood volume in the organism in attachment of a sensor to the organism can be removed to enable correct measurement. In a preferred embodiment of the present invention, light source means is formed by a plurality of first light source means for exposing vital tissue to first light of different wavelengths which are absorbed by specific dyes and second light source means for exposing the vital tissue to second light of a wavelength which is not absorbed by any specific dye. Input means is provided to input the dose quantity D (mg/kg) of each of different specific dyes, so that a corresponding light source means is selected from the plurality of first light source means in response to a currently inputted dose quantity, to apply light from the selected light source means to the vital tissue as first light. Thus, according to the preferred embodiment of the present invention, a prescribed light source can be automatically selected in response to the dose quantity of a specific dye, whereby measurement can be performed in the same accuracy with respect to any specific dye of any dose quantity, to effectively measure the index R MAX expressing the total amount of hepatic cell function. In a more preferred embodiment of the present invention, a blood plasma disappearance rate k and a liver removal ratio R = D x k are evaluated on the basis of an obtained coefficient of a simulation function. Thus, in the more preferred embodiment of the present invention, the blood plasma disappearance rate k and the removal ratio R are obtained while operation of the blood plasma disappearance rate k and the liver removal ratio R is performed a plurality of times by changing respective dose quantities of different specific dyes, thereby to obtain the index R MAX expressing the total amount of hepatic cell function on the basis of the plurality of dose quantities and removal ratios R thus obtained. These and other objects, features, aspects and advantages of the present invention will become more apparent from the following detailed description of the present invention when taken in conjunction with the accompanying drawings. BRIEF DESCRIPTION OF THE DRAWINGS Figs. 1 to 4 are diagrams for illustrating the principle of biocalibration employed in the present invention; Fig. 5 is a schematic block diagram showing the entire structure of an embodiment of the present invention; Fig. 6 illustrates timing for detecting quantities of light of wavelengths λ₁ and λ₂ after passage through a prescribed optical path in a measured object; Fig. 7 illustrates data stored in a RAM as shown in Fig. 5; Figs. 8A to 8E are flow charts for concretely illustrating the operation of the embodiment, in which Fig. 8A shows a data sampling subroutine, Fig. 8B shows a biocalibration mode, Fig. 8C shows an initialization mode and Figs. 8D and 8E show a measurement mode; Figs. 9 to 12 are illustrative of exemplary displays on a display part as shown in Fig. 5; Fig. 13 shows an example of a disappearance curve of specific dye measured in the present invention; Figs. 14 to 16 are diagrams for illustrating operation for measuring an index R MAX according to the present invention; Fig. 17 is a schematic block diagram showing the structure of another embodiment of the present invention; Fig. 18 illustrates distribution of absorbance of specific dyes; Fig. 19 illustrates data stored in a RAM shown in Fig. 17; Figs. 20A and 20B are flow charts for illustrating operation in a calibration mode and a measurement mode in another embodiment of the present invention; and Fig. 21 is a diagram for illustrating a conventional method of measuring an index R MAX . DESCRIPTION OF THE PREFERRED EMBODIMENTS Before explaining embodiments of the present invention, description is now made on the principle of biocalibration employed in the present invention. Figs. 1 to 4 are diagrams for illustrating the principle of the biocalibration in the present invention. It is assumed that symbols I₁ and I₂ indicate quantities of light having a wavelength λ₁ which is largely absorbed by a specific dye and light of a wavelength λ₂ which is not absorbed by the specific dye incident upon vital tissue, and symbols L₁ and L₂ indicate light quantities after passage through a prescribed optical path in the vital tissue. Relations between the incident light quantities I₁ and I₂ and the passing light quantities L₁ and L₂ in injection of the specific dye are as follows: (1) logI₁/L₁ = kg₁·Cg·Vb + f₁(Cb, Vb) + γt₁ (2) logI₂/L₂ = f₂(Cb, Vb) + γt₂ Respective coefficients and variables are shown in Fig. 1. Symbols f₁ and f₂ represent functions which are determined by characteristics of blood at the wavelengths λ₁ and λ₂. On the other hand, relations between the incident light quantities I₁ and I₂ and the passing light quantities L₁ and L₂ before injection of the specific dye are as follows: (3) logI₁/L₁ = f₁(Cb, Vb) + γt₁ (4) logI₂/L₂ = f₂(Cb, Vb) + γt₂ The relation between the passing light quantities L₁ and L₂ previous to actual injection of the specific dye is measured as shown in Fig. 2, to be in the linear relation shown in Fig. 3. This is the data in case of attaching a sensor to an organism and fluctuating the blood volume in the organism. It has been confirmed that such linearity has reproducibility, with no individual difference. Then, the expressions (3) and (4) would appear as follows: (5) logL₁ = AlogL₂ + B That is, the same can be expressed as follows, by using the expressions (3) and (4): (6) logI₁ - {f₁(Cb, Vb) + γt₁} = A[logI₂ - {f₂(Cb, Vb) + γt₂}] + B where Cb represents blood concentration in a sample and Vb represents blood volume in the sample. A function C obtained by multiplying concentration of the specific dye by the blood volume in the sample and the absorption coefficient of the specific dye by using the expressions (1) and (2) after injection of the specific dye can be expressed as follows: (7) C = logL₁ - [A·logL₂ + B] The function C is found by the expression (7) as follows: (8) C = logI₁ - kg·Cg·Vb - f₁(Cb, Vb) + γt₁ - A[logI₂ - {f₂(Cb, Vb) + γt₂}] - B Through the expression (6), we have: (9) C = -kg·Cg·Vb Hence, it is understood that a signal of the function C can be obtained by using Fig. 3 as a calibration curve. As to the function C, however, although the coefficient kg is constant, it can be considered that the blood volume Vb in each part is changed from time to time, and hence, if the blood volume Vb in a prescribed sample created by the sensor once attached is changed, the amount of the specific dye is also changed in proportion thereto although the dye concentration remains unchanged. This is typically shown in Fig. 4. Referring to Fig. 4, it is assumed that DE represents the value of the function C after a lapse of t₁ minutes. The blood contained in the prescribed sample obtained after a lapse of t₁ + Δt minutes is changed in volume, whereby an observation point is changed from E to E′. Assuming that Δt is sufficiently less than one minute, the specific dye concentration in the blood after the lapse of t₁ minutes may be considered identical to that after the lapse of t₁ + Δt minutes. However, as to the function C, the change is from C = DE to C′ = D′E′ . C ≠ C′ , and hence some correction must be performed. Hence, by normalizing DE and D′E′ at a point L₁₀, apparent fluctuation of the dye concentration due to the fluctuation of the blood volume can be corrected. When the specific dye is injected, a signal of only logL₁ is fluctuated, to lie to a point E, for example. At this time, DE becomes the function C as shown in the expression (9). The blood volume Vb in the expression (9) can be interpreted as being denoted by CD, and hence, normalizing the Y coordinate of a point A as L₁₀, the same is expressed as follows: Hence, a signal Cg corresponding to the specific dye concentration can be found by the expressions (7) and (10) as follows: Using the method of least squares, the function Cg of a simulation curve in time change of the aforementioned result Cg of calculation is expressed as follows: (12) Cg = Ae Bt where t represents the elapsed time after injection of the specific dye and symbols A and B represent constants. The constants A and B are found by the above expression (12). The blood plasma disappearance rate k and the liver removal ratio R are expressed as follows: (13) k = -B (14) R = K·D Then D is the dose quantities of a specific dye. While the biocalibration employed in the present invention has been described in the above, description is now made on an embodiment of the present invention employing the aforementioned biocalibration. Referring to Fig. 5, a liver function testing apparatus is formed by a sensor part 10 and a measurement processing part 200. The sensor part 10 includes a first light source 11, a second light source 12, a light receiving element 13 and a preamplifier 14. The first light source 11 and the second light source 12 generate optical pulses of a wavelength λ₁ having large absorbance to specific dye and optical pulses of a wavelength λ₂ having small absorbance, respectively. The light receiving element 13 receives light applied to vital tissue 15 from the light sources 11 and 12 to pass through a prescribed optical path. The light sources 11 and 12 are driven by the measurement processing part 200 to alternately emit light by pulse operation, respectively. The measurement processing part 200 includes a CPU 34 which serves as arithmetic means. The CPU 34 supplies a start signal to an oscillation circuit 24 and a timing circuit 23 through an I/O port 32. The oscillation circuit 24 regularly oscillates to produce a prescribed clock signal. This clock signal and the aforementioned start signal are utilized to supply constant currents i₁ and i₂ to the first light source 11 and the second light source 12 from a constant current circuit 21 through the timing circuit 23 and a decoder 22 at timing TM₁' and TM₁'' in Fig. 6. The light emitted from the first light source 11 and the light emitted from the second light source 12 pass through the prescribed optical path in the vital tissue 15, to be incident upon the light receiving element 13. A current generated from the light receiving element 13 is supplied to the preamplifier 14 to be subjected to current-to-voltage conversion, while being amplified to be supplied to the measurement processing part 200. Output of the preamplifier 14 is amplified to a level within a prescribed range by an amplifier 16 provided in the measurement processing part 200, whereby output such as V PD in Fig. 6 is obtained. A sample and hold circuit 28 samples and holds output from the amplifier 16 on the basis of a timing signal TM₂′, shown in Fig. 6, generated by the timing circuit 23 and a decoder 25. The signal thus sampled and held is selected by a multiplexer 29 and converted into a digital signal by an A-D converter 30, to be data-latched by a data latch 31. At this time, the multiplexer 29, the A-D converter 30 and the data latch 31 are controlled in timing by the timing circuit 23 and the decoder 26. The latched data are timed by a decoder 27 through a select signal outputted from the CPU 34 through the I/O port 32, to be taken in a RAM 35 as digital signals L₁ and L₂. The I/O port 32 is connected with a buzzer 33, which informs timing for injecting the specific dye. Further, the CPU 34 is connected with the RAM 35, a ROM 36, a display part 37, a function part 39 and an input part 45. The RAM 35 is adapted to store data as shown in Fig. 7 as hereinafter described, and the ROM 36 stores programs based on flow charts shown in Figs. 8A to 8E as hereinafter described. The display part 37 displays data as shown in Figs. 9 to 12, as hereinafter described. A printer 38 is adapted to print the result of a liver function test. The function part 39 includes an alarm LED 40, a calibration key 41, a start key 42 and a print key 43. The alarm LED 40 is adapted to display an alarm when reliability of the test result is small and the calibration key 41 is adapted to set a biocalibration mode, while the start key 42 is adapted to command start of a measurement mode and the print key 43 is adapted to command printout of the test result. The input part 45 is adapted to input the dose quantity of a specific dye. In the aforementioned exemplary structure shown in Fig. 5, the light emitted from the first and second light sources 11 and 12 to pass through the prescribed optical path in the vital tissue 15 is received by a single light receiving element 13. However, such means is not restricted to this but light receiving elements may be provided in correspondence to the first and second light sources 11 and 12 respectively to sample outputs of the respective light receiving elements, thereby to read the respective sampling outputs by the CPU 34 in a time-sharing manner. Alternatively, a single light source commonly emitting light having a wavelength λ₁ absorbed by specific dye and light having a wavelength λ₂ not absorbed by the same may be provided as light source means, with provision of two filters for individually transmitting the light of the respective wavelengths and light receiving elements corresponding to the respective ones of the filters. Fig. 7 illustrates data stored in the RAM 35 as shown in Fig. 5 and Figs. 8A to 8E are flow charts for illustrating concrete operation of the embodiment of the present invention, while Figs. 9 to 12 are illustrative of exemplary displays on the display part shown in Fig. 5, Fig. 13 is illustrative of an exemplary disappearance curve of specific dye and the result of R MAX measured in the present invention. With reference to Figs. 5, 8A to 8D and 13, description is now made on the concrete operation of the embodiment of the present invention. The operation of the inventive apparatus includes a data sampling mode, a biocalibration mode, an initialization mode and a measurement mode, and Figs. 8A, 8B, 8C, 8D and 8E show operation flows in these modes respectively. First, it is pointed out that the data sampling mode shown in Fig. 8A is executed as subroutines in the biocalibration mode and the measurement mode as hereinafter described. Steps (abbreviated as SP in the figures) SP11 to SP16 are adapted to sample quantities of light of a pair of wavelengths λ₁ and λ₂ after passage through a measured object and store the same in the RAM 35. Namely, the CPU 34 outputs the start signal through the I/O port 32 shown in Fig. 5 at the step SP11. The values L₁ and L₂ are data-latched by the start signal, as hereinabove described. The CPU 34 waits until the data are latched at the step SP12. Then, at the step SP13, the CPU 34 outputs the select signal to a select line shown in Fig. 5 through the I/O port 32, to read the data of L₁ through the I/O port 32 at the step SP14, thereby to store the same in a storage area 8a1 of the RAM 35 as shown in Fig. 7. Similarly, the CPU 34 stores the data of L₂ in a storage area 8a2 of the RAM 35 at the steps SP15 and SP16. Upon completion of the aforementioned operation at the step SP16, the CPU 34 returns to the original step. This will be described with reference to Fig. 8B showing the biocalibration mode and Figs. 8D and 8E showing the measurement mode. Fig. 8B shows the operation flow chart of the biocalibration mode, which is started upon power supply to the apparatus or upon completion of the operation of the measurement mode shown in Figs. 8D and 8E, as hereinafter described. At a step SP21, the CPU 34 makes the biocalibration mode appear on the display part 37. This display shows that the apparatus enters the biocalibration mode and indicates mounting of the sensor part 10 as shown in Fig. 9, for example. In accordance with this indication, an operator attaches the sensor part 10 to the vital tissue 15. Thereafter the CPU 34 waits until the calibration key 41 is operated at a step SP22. When the calibration key 41 is operated, the CPU 34 advances to a step SP23, to execute the data sampling subroutine shown in Fig. 8A, as hereinabove described. Then, the CPU 34 controls the constant current circuit 21 so that the data L₁ and L₂ read at the step SP23 are within ranges of light quantity data L MAX and L MIN stored in storage areas 8b1 and 8b2 of the RAM 35. The CPU 34 then stores current set values i₁ and i₂ in storage areas 8c1 and 8c2 in the RAM 35. Thereafter the currents i₁ and i₂ regularly flow to the light sources 11 and 12. Initializing operation for the aforementioned currents will be described in further detail with reference to Fig. 8C. Then, the CPU 34 sounds the buzzer at a step SP25, to inform that power setting is completed. Subsequent steps SP26 to SP29 are shown as a flow chart for performing the aforementioned biocalibration. In more concrete terms, the CPU 34 samples the values of L₁ and L₂ n times respectively at the steps SP26 and SP27, to make CL₁(1) to CL₁(n) stored in storage areas 8d1 to 8dn and CL₂(1) to CL₂(n) stored in storage areas 8e1 to 8en. At the subsequent step SP28, the CPU 34 performs regression line analysis with respect to logCL₁(I) and logCL₂(I) (I = 1 to n), in accordance with the following operation expression: logCL₁(I) = A·logCL₂(I) + B The CPU 34 finds the values A and B in the above operation expression, a correlation coefficient r₁ and the maximum value of CL₁(I) (I - 1 to n) as CL₁₀, to store the same in storage areas 8f1, 8f2, 8f3 and 8f4 in the RAM 35 respectively. Then, at the step SP29, the CPU 34 determines whether or not the correlation coefficient r₁ is at least 0.998 in order to verify reliability of the biocalibration, advances to a step SP30 if the same is less than 0.998 to light the alarm LED 40, and returns to the step SP22 to again perform biocalibration. On the other hand, if a determination is made that the correlation coefficient r₁ is at least 0.998, the CPU 34 advances to the measurement mode as shown in Fig. 8D. The reference value 0.998 of the correlation coefficient r₁ herein employed is a mere example, which is determined by performance of the entire apparatus. During the data sampling of n times at the step SP26, the testee raises and brings down his hand and suppresses the same by the sensor, in order to change the blood volume in the organism. With reference to Fig. 8C, the aforementioned initializing operation at the step SP24 as shown in Fig. 8B will now be described in more concrete terms. The light quantity data L₁ and L₂ of the light of the wavelengths λ₁ and λ₂ are stored in the storage areas 8a1 and 8a2 of the RAM 35. At a step SP241, the CPU 34 makes the values of L₁ and L₂ stored in storage areas 8h1 and 8h2 in the RAM 35 as L0λ₁ and L0λ₂ respectively. Then the CPU 34 executes steps SP242 to SP249, to adjust the set values of the currents flowing from the constant current circuit 21 so that L0λ₁ and L0λ₂ are set between the light quantity data L MAX and L MIN (L MAX > L MIN ) stored in the storage areas 8b1 and 8b2 of the RAM 35. In more concrete terms, if L0λ₁ is greater than L MAX at the step SP242, the CPU 34 advances to the step SP243 to set the current set value i₁ at a small value to again execute the steps SP23 and SP241, and a determination is again made as to whether or not L0λ₁ is greater than L MAX at the step SP242. If L0λ₁ is less than L MAX , the CPU 34 advances to the step SP244 to determine whether or not L0λ₁ is less than L MIN . If L0λ₁ is less than L MIN , the CPU 34 increases the value of the current set value i₁ at the step SP245, to return to the aforementioned step SP23. This operation is repeated to set the current set value i₁ so that L0λ₁ is between L MAX and L MIN . Then, at the steps SP246 to SP249, the current set value i₂ is set so that L0λ₂ is between L MAX and L MIN , similarly to the steps SP242 to SP245. Thus, the current set values i₁ and i₂ finally set at the steps SP23 to SP249 are stored in the storage areas 8c1 and 8c2 of the RAM 35. With reference to Figs. 8D and 8E, description is now made on the measurement mode. At a step SP41, the CPU 34 makes a display for injection of the specific dye on the display part 37. As to this display, indication is made for injection of the specific dye such as ICG as shown in Fig. 10, for example. In accordance with the display, the operator prepares for injection of the specific dye to the testee. At this time, the input part 45 inputs the dose quantity of the specific dye, e.g., 2 mg/kg as D₁, which is stored in a storage area 8j of the RAM 35. At a step SP42, the CPU 34 waits until the start key 42 is operated. Upon a determination that the start key 42 is operated, the CPU 34 displays timing for injecting the specific dye at a step SP43, while sounding the buzzer 33. This is displayed as 1 → 2 → 3 → 4 → 5 as shown in Fig. 11, for example, so that the measurer injects the specific dye upon display of "5". The CPU 34 generates a first sound from the buzzer 33 with the displays of "1", "2", "3" and "4", while generating a different sound from the buzzer 33 upon display of "5". Upon generation of the sound and the display, the measurer injects the specific dye. The CPU 34 sets "0" as the initial value of a timer at a step SP44. Then, at a step SP45, the CPU 34 executes a data sampling program, which is the subroutine as hereinabove described with reference to Fig. 8A. Then, the sampling data are stored in the storage areas 8a1 to 8a2 of the RAM 35 as L₁ to L₂, respectively. At a step SP46, the CPU 34 performs operation based on the following operation expression by using the coefficients A, B and CL₁₀ stored in the storage areas 8f1, 8f2 and 8f4 of the RAM 35 in the biocalibration mode as hereinabove described with reference to Fig. 8B, to store Cg(I) in a storage area 8g1 of the RAM 35: The value of Cg(I) is displayed on the display part 37 at the step SP46 in a mode shown in Fig. 12, for example. Referring to Fig. 12, the axis of abscissa indicates the elapsed time from injection of the specific dye and the axis of ordinate indicates the value of Cg(I). Assuming that m represents the sampling number of a disappearance curve of the specific dye, symbol I indicates integers 1 to m and assuming that T s represents a measuring time of the disappearance curve, a single sampling time is ITM = T s /(m - 1) . The same coincides with the injection time of the specific dye in the case of I = 1, as a matter of course. At a step SP47, the CPU 34 waits during this sampling time ITM. Upon a lapse of this standby time, the CPU 34 judges whether or not i is greater than m at a step SP48. The CPU 34 advances to a step SP49 if i is greater than m , while the same again returns to the step SP45 to repeat sampling if the former is less than the latter. The data Cg(I) stored in the storage areas 8g1 to 8gm of the RAM 35 draw a disappearance curve of the specific dye as shown in Fig. 13, for example, and the leading edge thereof is detected so that data preceding the same are subtracted as baselines from the respective values of Cg(I) at a step SP49, to be again stored in the storage areas 8g1 to 8gm. Needless to say, L₁ to L₂ at the step SP45 may be average values of k times, in order to improve the accuracy of measurement. Then, at a step SP51, the CPU 34 finds the constants A₁ and B₁ by using the method of least squares in a simulation curve of: Cg(I) = A₁ x e B 1 xI I = Ts/(m - 1) (min.) with respect to data between times T₁ to T₂ (0 < T₁ < T₂ < Ts) within the data Cg(I) stored in the storage areas 8g1 to 8gm. At a step SP57, the CPU 34 evaluates K₁ from K₁ = -B₁ while evaluating a correlation coefficient r g1 , to store the same in storage areas 8k1 and 8k2 of the RAM 35. Similarly, the CPU 34 evaluates constants A₂ and B₂ in a block between times T₃ and T₄ at a step SP58, and evaluates a coefficient K₂ and a correlation coefficient r g2 at a step SP59 to store the same in the storage areas 8k3 and 8k4. The CPU 34 further operates constants A₃ and B₃ in a block between times T₅ and T₆ at a step SP60 and evaluates a coefficient K₃ and a correlation coefficient r g3 at a step SP61, to store the same in the storage areas 8k5 and 8k6. Then the CPU 34 operates the index R MAX at a step SP62. The times T₁ to T₆ and the coefficients K₁ to K₃ are mapped in relation as shown in Fig. 14. The CPU 34 assumes that C g1 , C g2 and C g3 represents values corresponding to specific dye concentration values at the times T₁, T₃ and T₅ with the assumption that R i = C gi x K i , to display the graph shown in Fig. 15. Referring to Fig. 15, the axis of abscissa is indicated by 1/Cg and the axis of ordinate is indicated by 1/R. On the basis of these data, the CPU 34 operates a and b by using the method of least squares, through the following operation expression: 1/R i = a(1/C gi ) + b (i = 1, 2, ..., m, m ≧ 2, where i = 1 is a first block) Then, the CPU 34 operates the index R MAX and r MAX in accordance with the following operation expression, to store the same in the storage areas 8ℓ1 and 8ℓ2 of the RAM 35: R MAX = 1/b Y MAX is the coefficient of correlation. Although three times blocks are provided in the above embodiment, such time blocks may be in any number so far as the same is at least two, and accuracy is improved as the number of times blocks is increased. Although 1/Cg₁, 1/Cg₂ and 1/Cg₃ are plotted in the axis of abscissa in Fig. 15, this is a simplified type and the index R MAX can be more correctly measured by evaluating the coefficient A₁ on the basis of the following operation expression to assume the coefficient A₁ as a coefficient C₀₁, thereby to create the data as shown in Fig. 14. Assuming that T₁ = 5 min. and the dose of ICG is D₁ mg/kg, C O1 may correspond to D₁, D₂ may be equal to D₁·C g2 /C O1 and D₃ may be equal to D₁·C g3 /C O1 , where R i = D i x K i . D₁ may be previously set at 2 mg/kg, for example, as a value specific to the apparatus, or may be inputted by the input part 45. Then, at a step SP53, the CPU 34 determines whether or not a correlation coefficient r gn is less than 0.95, for example. This is to check the degree of correlation, since correlation is improved as the correlation coefficient r gn approaches -1. However, a value -0.95 is a provisional value between zero to -1, and reliability of the apparatus is improved as the value approaches -1. The CPU 34 determines that reliability is small if the correlation coefficient r gn is greater than 0.95, for example, to turn on the alarm LED 40 at a step SP54. When the CPU 34 determines that the correlation coefficient r gn is less than -0.95, for example, and measurement is reliable at the step SP53, on the other hand, the CPU 34 advances to a step SP55 without flashing the alarm LED 40. At the step SP55, the CPU 34 determines whether or not the print key 43 is operated, to make the printer 38 print the value of R MAX if the same is operated. If necessary, the CPU 34 makes the printer 34 also print the specific dye disappearance curve of Cg(I) stored in the storage areas 8g1 to 8gn of the RAM 35, to shift to the aforementioned biocalibration mode shown in Fig. 8B. Upon a determination that the print key 43 is not operated at the step SP55, the CPU 34 also shifts to the biocalibration mode. According to the embodiment of the present invention as hereinabove described, vital tissue is expected to first light of a wavelength absorbed by a specific dye dosed into the blood of the vital tissue to be taken in and removed by the liver and second light of a wavelength not absorbed by the specific dye and first and second photoelectric conversion signals corresponding to the first light and the second light obtained from the vital tissue are sampled so that the coefficient of a regression line expression between the first and second photoelectric conversion signals is determined on the basis of variable components in the blood included in the sampled first and second photoelectric conversion signals, thereby to operate a value correlated with specific dye concentration in the blood on the basis of a sampling signal during a prescribed period after injection of the specific dye and the determined coefficient of the regression line expression. Thus, the index R MAX can be measured by performing ICG injection only once with no blood collection, whereby mental and physical burdens on the testee can be extremely reduced. Further, artifacts such as blood flow disturbance, vibration of the organism, pulsation in the organism and change of the blood volume in the organism in attachment of the sensor can be removed to enable correct measurement. Fig. 17 is a schematic block diagram showing another embodiment of the present invention, and Fig. 18 illustrates absorbance distribution of specific dyes. The embodiment shown in Fig. 17 is structured similarly to that shown in Fig. 5, except for the following points: A function part 39 of a measurement processing part 200 is provided with an input part 44 for inputting a dose quantity D. A sensor part 10 is formed by first light sources 111, 112, ..., 11m, a second light source 20, a light receiving element 13, a preamplifier 14 and an analog switch 50. The first light sources 111, 112, ..., 11m are adapted to expose vital tissue 15 to optical pulses of wavelengths which are absorbed by specific dyes dosed into the blood of the vital tissue 15 to be taken in and removed by the liver. In other words, the first light sources 111, 112, ..., 11m respectively emit light of wavelengths λ₁₁, λ₁₂, ..., λ 1m of large absorbance along absorbance distribution of the specific dyes as shown in Fig. 18, for example. The analog switch 50 selects one of the first light sources 111, 112, ..., 11m in response to the dose quantity inputted from the input part 44 to feed a current i₁ to the same, thereby to make the selected light source generate a first optical pulse of a wavelength λ i . At this time, a CPU 34 controls the analog switch 50 through an I/O port 32 and si₃, to select the light source. The second light source 20 exposes the vital tissue 15 to a second optical pulse of a wavelength λ₂₀ which is not absorbed by the specific dye. One of the first light sources 111, 112, ..., 11m and the second light source 20 are driven by the measurement processing part 200 to emit light alternately in pulse operation. The light receiving element 13 receives the first optical pulse applied from one of the first light sources 111, 112, ..., 11m to the vital tissue 15 and passing through a prescribed optical path to output light receiving output L i , while receiving the second optical pulse applied from the second light source 20 and passing through a prescribed optical path, to output light receiving output L₂. Fig. 19 illustrates data stored in a RAM 35 shown in Fig. 17, Fig. 20A is a flow chart for illustrating operation of a biocalibration mode in the second embodiment of the present invention, and Fig. 20B is a flow chart for illustrating operation of a measurement mode. The biocalibration mode shown in Fig. 20A is started upon power supply to the apparatus or completion of operation of the measurement mode, similarly to the aforementioned first embodiment. At a step SP19, the CPU 34 makes a display part 37 display that an ICG dose quantity must be inputted. An operator recognizes this display, to input the ICG dose quantity D from the input part 44 shown in Fig. 17. This ICG dose quantity D is stored in a storage area 8j1 of the RAM 35. The CPU 34 switches the analog switch 50, in order to select a first light source corresponding to the inputted ICG dose quantity D. The CPU 34 so switches the analog switch 50 as to select a light source of a wavelength λ₁₁ when a dose quantity of 0.1 to 0.5 mg/kg is inputted, for example, while selecting a light source of a wavelength λ₁₂ when a dose quantity of 0.5 to 1 mg/kg is inputted, for example. Operation at steps SP21 to SP30 is identical to that described above with reference to Fig. 8B. The measurement mode is now described with reference to Fig. 20B. Upon completion of the processing at the steps SP41 to SP49 shown in Fig. 8D, the CPU 34 advances to a step SP71 shown in Fig. 20B. At the step SP71, constants A and B are obtained by simulation curves through use of the method of least squares, similarly to the aforementioned step SP51 shown in Fig. 8E. At a step SP72, the CPU 34 obtains a blood plasma disappearance rate k and a liver removal ratio R by operating k = -B and R = K·D . The CPU 34 makes the obtained values k and R stored in storage areas 8j2 and 8j3 of the RAM 35. At this time, the CPU 34 operates a correlation coefficient r₂ by the method of least squares, to make the operated correlation coefficient r₂ stored in a storage area 8j4 of the RAM 35. Further, the CPU 34 makes a buzzer 33 sound completion at this time. The CPU 34 makes the values k and R and the dose quantity D appear on a display part 37, for example. Then, the CPU 34 determines whether or not the correlation coefficient r₂ is less than 0.95, for example, at a step SP73. This is to check the degree of correlation, since correlation is improved as the correlation coefficient r₂ approaches -1. However, a value -0.95 is a provisional value in zero to -1, and reliability of the numerical values is improved as the said value approaches -1. If the correlation coefficient r₂ is greater than 0.95, for example, the CPU 34 determines that reliability is small, to turn on an alarm LED 40 at a step SP74. If the correlation coefficient r₂ is less than -0.95, for example, to cause a determination that measurement is reliable at a step SP73, the CPU 34 advances to a step SP75 without flashing the alarm LED 40. The CPU 34 determines whether or not a print key 43 is operated at a step SP55, to make a printer 38 print the value k , R and D if the same is operated. If necessary, the CPU 34 makes the printer 38 also print a specific dye disappearance curve of Cg(I) stored in storage areas 8g1 to 8gn of the RAM 35, to shift to the aforementioned biocalibration mode shown in Fig. 20A. If a determination is made that the print key 43 is not operated at the step SP75, the CPU 34 also shifts to the biocalibration mode. After the blood plasma disappearance rate k and the liver removal ratio R are thus obtained, ICG is again injected in a different dose quantity on the next day and the aforementioned series of operation is repeated to obtain D₂ and R₂. Further, ICG is newly injected on the day after next, to obtain D₃ and R₃. The inverse numbers 1/D of the dose quantities D and the inverse numbers 1/R of the liver removal ratios R are plotted as shown in Fig. 16 to draw a regression line, thereby to easily evaluate 1/R MAX by obtaining the intersection point of the regression line and 1/R. According to this embodiment, as hereinabove described, a prescribed light source is automatically selected in response to the dose quantity of the specific dye, whereby measurement can be performed in the same accuracy with respect to any specific dye of any dose quantity, to effectively measure the index expressing the total amount of hepatic cell function.

Claims: A liver function testing apparatus for testing liver function, comprising: a plurality of first light source means (111, 112, ..., 11n) for exposing said vital tissue to first light of different wavelengths absorbed by said specific dye, and second light source means (20) for exposing said vital tissue to second light of a wavelength not absorbed by said specific dye, input means (45) for inputting respective dose quantities D (mg/kg) of different specific dyes, light source selection means (50) for selecting corresponding light source means from said plurality of first light source means in response to a dose quantity currently inputted by said input means to apply light from selected said light source means to said vital tissue as said first light, photoelectric conversion means (13) for outputting first and second photoelectric conversion signals corresponding to said first light and said second light applied to said vital tissue by said light source means and obtained from said vital tissue; sampling means (28) for sampling said photoelectric conversion outputs from said photoelectric conversion means; decision means (34, SP28) for obtaining first constants A and B by performing the regression line analysis in accordance with the following operation expression: log CL₁ = A · logCL₂ + B assuming that CL₁ and CL₂ represent values of said first and second photoelectric conversion signals sampled by said sampling means a plurality of times before injection of said specific dye; arithmetic means (34, SP28) for obtaining, on the basis of the constants A and B obtained by said decision means, a value Cg correlated with said specific dye concentration in accordance with the following operation expression: wherein CL₁₀ represents the maximum value of said first photoelectric conversion signals, and assuming that t represents a prescribed period after injection of said specific dye, obtaining constants A₁ and B₁ by using the method of least squares on the basis of a simulation curve in accordance with the following operation expression: and obtaining a blood plasma disappearance rate k and retention rate R% in said time t in accordance with the following equations: k = -B₁ and means (34) for obtaining an index R max expressing the total amount of hepatic cell function on the basis of said coefficient of said simulation function obtained by said arithmetic means. A liver function testing apparatus in accordance with claim 1, wherein said arithmetic means includes means (SP72) for obtaining a blood plasma disappearance rate k of said specific dye and a liver removal ratio R = D x k on the basis of obtained said coefficient of said simulation function. A liver function testing apparatus in accordance with claim 1, wherein said means for obtaining said index includes means (SP51, 57-62) for injecting said specific dye, dividing a prescribed time interval from uniform distribution of said specific dye in said blood into a plurality of blocks to obtain coefficients A i and B i on the basis of simulation functions Cg = A i ·e Bit (i = 1, 2, ..., m, m ≧ 2, where i = 1 is a first block) in respective said blocks and to obtain values of Cg in initial times of respective said blocks as C i assuming that K i = -B i and performing regression line analysis on the basis of obtained said coefficients K i and C i by an operation expression of (1/K i ·C i ) = a(1/C i ) + b to obtain coefficients a and b , thereby to obtain said index R MAX on the basis of an operation expression of R MAX = 1/b . A liver function testing apparatus in accordance with claim 1, wherein said means for obtaining said index includes means for injecting said specific dye, dividing a prescribed time interval from uniform distribution of said specific dye in said blood into a plurality of blocks to obtain coefficients A i and B i on the basis of simulation functions of Cg = A i ·e Bit (i = 1, 2, ..., m, m ≧ 2, where i = 1 is a first block) in respective said blocks and to obtain, on the basis of obtained said coefficients A i and dose quantity D₁ of said specific dye, D i by an operation expression of D i = D i ·C i /A₁ (i ≧ 2, where D i is a first block and C i is a value of Cg in the first time of each block) assuming that K i = -B i and performing regression line analysis from an operation expression of (1/K i ·D i ) = C(1/D i ) + d on the basis of obtained K i and D i to obtain coefficients C and d , thereby to obtain said index R MAX from R MAX = 1/d . A liver function testing apparatus in accordance with claim 1, wherein said decision means includes means (34) for operating a correlation coefficient of said regression line expression. A liver function testing apparatus in accordance with claim 5, further including informing means (33) for giving an alarm when said correlation coefficient operated by said means for operating said correlation coefficient is greater than a predetermined value. A liver function testing apparatus in accordance with claim 1, wherein said arithmetic means includes means (34) for operating a correlation coefficient of said simulation function. A liver function testing apparatus in accordance with claim 1, further including informing means (33) for giving an alarm when said correlation function of said simulation function is greater than a predetermined value. A liver function testing apparatus in accordance with claim 1, further including mode selection means (41, 42) for selecting a biocalibration mode for performing operation for deciding said coefficient of said regression line expression by said decision means and a measurement mode for performing operation for operating said value correlated with said specific dye concentration by said arithmetic means. A liver function testing apparatus in accordance with claim 9, further including means (34) for activating said decision means in response to selection of said biocalibration mode by said mode selection means. A liver function testing apparatus in accordance with claim 9, further including means (34) for activating said arithmetic means in response to selection of said measurement mode by said mode selection means. A liver function testing apparatus in accordance with claim 1, further including set means (SP241 - SP249) for setting intensity levels of said first light and said second light emitted from said light source means so that levels of said first and second photoelectric conversion signals are within a predetermined range. A liver function testing apparatus in accordance with claim 1, further including output means (37, 38) for outputting said operated index R MAX .

Inventors: AWAZU KUNIO C O OSAKA WORKS, KANDA MASAHIKO C O OSAKA WORKS, AWAZU, KUNIO C/O OSAKA WORKS, KANDA, MASAHIKO C/O OSAKA WORKS
Applicants: SUMITOMO ELECTRIC INDUSTRIES, SUMITOMO ELECTRIC INDUSTRIES, LTD.
Application year: 1988
Main classification: A61B5
IPC codes: A61B5