JPS60105956A - Quantitative analizer of blood compoment - Google Patents

Abstract

PURPOSE:To minimize detection errors by performing a computation in comparison of the output quantity of electricity of an electrode for detecting material to be detected (electrode for material being detected) with the reference quantity of electricity in quantitative analizer of glucose, chloesterol and the like in blood to supplement deterioration in the electrode for material being detected. CONSTITUTION:A carrier liquid 29 is run into a sensor 34 and blood to be detected is put into an injector 45 to flow to an electrode for detecting interferring substance (electrode for interferring substance) 38 via the electrode 37 for the material being detected. Then, the difference is computed between the output quantity of electricity of the interferring substance and that of the electrode 37 for material being detected and a blood sugar value is displayed. Aside from this, the output quantity of electricity of the electrode 37 for material being detected is used as the reference quantity of electricity for the material being detected (for example, glucose 100% solution). When the output quantity of electricity of the electrode 37 for material being detected in a measuring blood is compared with the reference quantity of electricity and it deteriorates more than a specified value, a signal display 44 is done to amplify or replace the electrode 37 for material being detected. Thus, the detirioration in the electrode 37 for material being detected can be supplemented correctly and the difference between the material being detected and the interferring substance in the blood can be detected and the interferring substance in the blood can be detected without error.

Description

[Detailed Description of the Invention] [Technical Field] The present invention enables the determination of test substances such as glucose, cholesterol, and uric acid in blood by eliminating the effects of interfering substances that cause errors in the determination of these test substances. Contains information related to blood component quantification meters performed in various states.

[Background technology]

Conventionally, when a biosensor, that is, an electrode for detecting an analyte and an electrode for detecting an interfering substance, deteriorates, the amount of electricity generated decreases, and an amplifier that amplifies the amount of electricity is used in areas that are not linear. There is a risk that the error will become large. Furthermore, users also lacked confidence in the sensor, and even though the sensor had not completely deteriorated, they replaced it with a new one, resulting in a large waste of money.

In addition, there is a known method of determining the deterioration state of the analyte detection electrode and interfering substance detection electrode by the number of times they have been used or the length of time they have been used. However, with the method of determining the number of times of use, there is variation among individual sensors. For example, some sensors deteriorate after 2000 times, while others start to deteriorate after 1900 or 2100 times, and the number of sensor replacements exceeds the specified number of times. Deterioration occurs quickly, causing errors in measured values,
Alternatively, there were cases where the item was replaced while it was still in a usable condition, which was very cumbersome.

On the other hand, in the method of determining the amount of time used, the state of deterioration of the sensor changes depending on the number of times the sensor is used within a predetermined designated time for sensor replacement, which has the same problem as the method of determining the number of times of use.

[Purpose of the invention]

An object of the present invention is to provide a blood component quantitative meter that can accurately detect the deterioration state of a sensor, that is, an electrode for detecting an analyte, and take appropriate measures.

[Disclosure of the invention]

The blood component quantification meter of the present invention includes a flow path through which a carrier liquid for a test substance flows, an injection port for the test substance into the flow path, and a test substance inserted into the flow path downstream of the injection port. Detection electrodes, interfering substance detection electrodes, and analyte detection electrodes! A blood component quantitative meter comprising: a calculation section that corrects the output electricity amount of the pole based on the output electricity amount of the NtM for detecting interfering substances; and a display section for displaying the calculation results of the calculation section, Comparing means for comparing the amount of electricity output from the test substance detection electrode with a reference amount of electricity for detecting the state of deterioration of the electrode for detecting the analyte and outputting a signal when the comparison results in a predetermined state of deterioration, A response means is provided which inputs the output signal from the comparison means and performs a predetermined anti-deterioration operation.

The configuration of this invention includes at least one of the following three embodiments.

(1) The reference quantity of electricity is set to an amount corresponding to an intermediate state between a normal usage state of the analyte detection electrode and an unusable deteriorated state, and the response means is set to an amount corresponding to an intermediate state of the analyte detection electrode. If configured to increase the amplification factor of the output electrical quantity.

In this case, the electrode for detecting the analyte has deteriorated to some extent, but it can still be used. However, due to the deterioration, the measurement accuracy will decrease if the amplification factor used up until then is increased, so the amplification factor is increased.
In other words, the aim is to increase sensitivity to counter deterioration and maintain measurement accuracy as high as possible.

(2) In the case of (1) above, the response means is provided with an alarm in addition to the amplification factor increasing means.

In this case, the user can be informed by the alarm that the sensitivity has been switched.

(3) The reference electrical quantity is 1 for detecting the analyte! In the case where the amount is set to an amount corresponding to the state of unusable deterioration of the pole, and the response means is configured as an alarm.

In this case, the user can accurately know from the alarm that the deterioration of the analyte detection electrode has progressed considerably and that it is time to replace it.

Note that the alarm device referred to in (2) and (3) is a general term for lamps (lit or flashing), buzzers, indicators, etc. Furthermore, since the state of deterioration of the interfering substance detection electrode is the same as that of the analyte detection electrode, they may be replaced at the same time.

A first embodiment of the present invention will be described with reference to FIGS. 1 to 5.

FIG. 1 is a block diagram of detection, calculation, and display of a test substance. 20 is a constant voltage generation circuit, 21 is for detecting the analyte! 23A is a current detection unit for the pole b; 22 is a current detection unit for the interfering substance detection electrode;

23B is the first stage layer width circuit, 24A, 24B l-j
:2nd stage layer width circuit, 24C and 24D are bypass lines, 2
5A, 25B are filter circuits, 26A, 26B
27 is an arithmetic circuit (arithmetic unit), and 28 is a display unit. The arithmetic circuit 27 calculates the amount of electricity detected (
Digital quantity) a and detected electrical quantity of interfering substance (digital quantity)
Calculation 5=n-b is performed based on b, and the display section 28 digitally displays the calculated value S.

FIG. 2 is an overall configuration diagram of the blood component quantitative meter.

This quantitative meter is composed of a storage tank 30 for a carrier liquid (buffer solution) 29, a metering pump 31, an injector 32, a liquid flow damper 33, a sensor section 34, a Li liquid tank 35, and a flow path 36 that connects these in order. There is. Sensor part 3
4 is an electrode 37 for detecting a test substance, and a W pole 3 for detecting an interfering substance.
8 and counter electrodes 39 thereof, each of which is connected to a constant pressure generating circuit (cell) 20.20 via an ammeter 40.40. It also has an input section 41 for analog data, which is the detection current, and a two-stage sensitivity switching circuit 42, which is connected to the central processing unit of the 8-bit microcomputer via the Φ conversion circuit 26 (26A, 26B in Fig. 1). CPU) 27 (calculation circuit 27 in Fig. 1), and is further connected to an LED (light emitting diode) driver 4.
3 to the digital display section 28 and various high lot display sections 44. 45 is a syringe for injector 32;

FIG. 3 shows the front panel 51 of the main body of the quantitative meter.

This front panel 51 includes a digital display section 28, various pilot I/display sections 44, a solution containing 100% of the test substance '14 (first standard solution), a solution containing only interfering substances (second standard solution, test substance O% ) and the test substance solution (sample solution), a common injection port 46 (this is in the injector 32), a connection port 47 for the carrier liquid suction tube (part of the flow path 36), a waste liquid tube (part of the flow path 36) A connection port 48, a power switch 49, and a pump switch 50 are provided. The pilot display unit 44 shows injection waiting instructions 44a1, measuring 44b, and first reference liquid injection instructions 44, which are IJD, respectively.
e, second standard solution injection instruction 44d, sample solution injection instruction 44
Display sections e and 44t° for sensor replacement instructions are provided.

Next, an explanation will be given of the operation when determining the blood sugar level, that is, glucose using this quantitative meter.

(2) When the power switch 49 is turned on, the metering pump 31 is activated, and the carrier liquid 29 having a pH of about 7.5 flows into the channel 36. The flow rate is 3 A/min. Until the carrier liquid 29 reaches the sensor section 34, the injection wait instruction L 44111 lights up (about 2 minutes).

■ When the carrier liquid 29 reaches the sensor section 34, the LFJ
) 44n goes out, and IJD44 instructs to inject the first reference solution.
c lights up. Accordingly, a 100% glucose solution, which is the first reference solution, is injected into the injection port 46. This turns off the LED 44c and turns off the LED 44b during measurement.
lights up. The output from the analyte detection electrode (i.e. immobilized enzyme electrode) 37 is obtained and displayed on the digital display 28 as, for example, 250 (a=25O[q/di
) ). There is no output from 11fi38 for interfering substance detection. The sensitivity of the electrode 37 to glucose at this time is stored in the memory of the microcomputer.

Note that when the sensitivity of the electrode 37 becomes low, the LED 440 lights up, so the 100% glucose solution is injected again.

When the IJD 44c lights up, the analog circuit automatically switches to a circuit with a higher amplification factor in the two-stage sensitivity switching circuit 42.Also, when the sensitivity is very low, the LED 44f, which instructs sensor replacement, lights up. , the sensor section 34 is replaced accordingly.

The specific configuration and operation of the two-stage sensitivity switching circuit 42 will be described later.

■ When the sensitivity of the electrode 37 is appropriate, the LED 44e does not light up, and the LED 44 (l) indicating the injection of the second reference solution lights up. Accordingly, the interfering substance (for example, ascorbic acid or uric acid) that is the second reference solution is detected. A 100% solution is injected into the injection hole 46. This turns off the LBD 44d and turns on the LED 44b during measurement. Outputs from both the immobilized enzyme electrode 37 and the interfering substance detection electrode 38 are obtained.

If the sensitivity of the two electrodes 37, 38 is the same, the output is the same, and is displayed on the digital display 28 as, for example, 7° (b = 70 [4/dJ?]). However, normally the two sensitivities are different and the sensitivity is adjusted.

The sensitivity of each electrode 37, 38 to the interfering substance at this time is stored in the memory of the microcomputer.

Based on the above, the first. Both electrodes 37°38 with the second reference solution
The calibration of the sensitivity is completed. Then, the calibrated numerical value is displayed on the digital display section 28, such as 70 (
b = 70 Cq/dl]).

■ After the above display, IJD446, which instructs sample solution injection.
lights up. In accordance with this, blood as a sample solution (test substance) is injected from the injection port 46. As a result, output is obtained to the two electric terminals i37 and 38, and the microcomputer C
PU (arithmetic circuit, arithmetic unit) 27 = 79 = a - b
is calculated, and the result is S, that is, glucose% (l
d/medium blood sugar level q) is displayed on the digital display section 28. However, the values of n and b at this time are 8 (-
250) and b (=70). This is because the composition differs depending on blood.

Note that when the two electrodes 37 and 38 have different sensitivities to interfering substances, the sensitivity adjustment is performed based on the sensitivity memorized in .

FIG. 4 shows the two-stage sensitivity switching circuit 42 and its peripheral circuits, and FIG. 5 is its time chart.

A peak hold circuit 55 and a first comparator 56 are connected to the output terminal a of the first stage layer width circuit 23A for the analyte detection current. The peak hold circuit 55 includes an operational amplifier 57. Dio-VB2° reset transistor sc+, constant voltage? [[Capacitor 60. [It is composed of a field effect transistor 61 and the like.]

The output terminals of the peak hold circuit 55 are connected to the second and third comparators 62 and 63.

Reference voltage ■ of the second comparator 62. is arbitrarily set to a level higher than the voltage level at which sensitivity is required. The reference voltage of the third comparator 1 and Notarro 3 is set at a level higher than the voltage level at which the test substance detection electrode 37 deteriorates and becomes unusable, and lower than the reference voltage vU. .

Output terminal e of these comparators 62,63.

f are both connected to the NOR circuit 64, and the output terminal g of the NOR circuit 64 is connected to D7. The lip 70 is connected to the knob 65. The output terminal i of the D-flip 70 knob 65 is connected to the base of the transistor 67 for operating the two-stage sensitivity switching relay 66A for the test substance and the operating transistor (not shown) for the three-stage sensitivity switching relay 66B for the interfering substance. Base, and 44 LEDs that also serve as sensitivity switching indicators (
It is connected to the base of the + operating transistor 68.

The output terminal d of the comparator 56 of the previous EQ 83 ] is connected to the NOT circuit 69 , and the output terminal 1 of the ) circuit 69
1 is connected to the clock input terminal of the D flip 70 tube 65. The output JJ terminal d of the comparator 56 is connected to a differentiating circuit 72 consisting of a capacitor 70 and a resistor 71, which is connected to the base of the reset transistor 59 and the reset terminal of the D flip-flop 165.

This comparator 56 is for detecting when the sample solution starts flowing and when all the sample solution has finished flowing, and the reference voltages □ and ef are almost ground (G
ND ) level, and even if the detection electrode 37 deteriorates and the generated voltage becomes considerably low, the comparator 56 will always
is now working. From the above, the magnitude relationship of each reference voltage is ■ref <■L < VU.

Next, the operation will be explained.

(1) Detection type 41! When i37 is a stop layer ((1 in Fig. 5)
) When the sample solution flows in, the voltage at the output terminal a of the first stage layer width circuit 23A increases, and this becomes the reference voltage (2). If the signal is higher than A, the output terminal of the first comparator 56
1-bell, which momentarily makes the reset I transistor 59 conductive through the differentiating circuit 72, and the capacitor 60f:
Let it discharge. However, immediately after that, charging starts again and the voltage at the output terminal C of the peak hold circuit 55 changes to the output terminal 3.
The voltage rises at the same level as the voltage (time t□~1.).

At time t□ when the peak hold circuit 55 is reset, the voltage at the output terminal e of the second comparator 2 goes from high level to low level, and the voltage at the output terminal f of the third comparator 63 tj: tff low level The voltage at the output terminal of the NOT circuit 69 becomes a high level and a low level.

The voltage at terminal C is determined by the third comparator 6 at time t2.
3, the voltage at the output terminal f of the comparator 63 becomes low level. Furthermore, the voltage at the terminal C rises to the reference voltage of the second comparator 62 at time t3. , and reaches its peak at time t4. At time t3 when the reference voltage ■U is exceeded, the voltage at the terminal C of the second comparator 62 becomes high level.

That is, from time t2 to time t3, since the voltages at terminals e and f of both comparators 62 and 63 are both at low level, the voltage at output terminal g of NOR circuit 64 is at high level. After time t3, the voltage at the output terminal g becomes low level. From time t2 to time t3, the voltage at the terminal g becomes high level, but since the voltage at the terminal remains low level, no clock is applied to the D flip 70 and 65, and therefore the voltage at the output terminal i is remains at low level.

After time t4, the voltage at terminal a decreases, but the voltage at terminal 0 is maintained at the peak voltage (〉■U), so terminal e,
The state of the voltage at f does not change, and the voltage at terminal g remains at a low level. Then, at time t5, when the voltage at the terminal a falls below the reference voltage vref, the voltage at one terminal C becomes low level, and the voltage at the other terminal becomes high level, and at the rising edge, the D7 lip flop 65
is clocked to read the state of terminal g, but since terminal g is at low level at this time, the D flip-flop 65
does not change, and the voltage at terminal i remains at low level.

That is, when the detection electrode 37 is normal, the relay 66A
, 66B and transistor 68 are inoperative.

(2) Detection t! ! , when the pole 37 has deteriorated to some extent and the sensitivity needs to be increased (see (2) in FIG. 5), the voltage at terminal a is the reference voltage ■r. , the operation at time t6 exceeding (1
), and the operation at time t7 when the voltage at terminal C exceeds the reference voltage ■ is the same as the operation at time t in (1).
The operation is the same as in 2.

At time t8 when the voltage at terminal a reaches its peak, the voltage at terminal C reaches the reference voltage ■ due to electrode deterioration. , and is held at a voltage between vL and ■□. Therefore, the voltage at terminal e remains low level after time t5,
Since the voltage at the terminal f maintains a low level after time tヤ, the terminal g of the NOR circuit 64 maintains a high I/bell level after time t7.

The voltage at terminal a decreases, and at time t9, the reference voltage Vr
When the voltage falls below ef, the terminal d becomes low level, and the terminal d becomes high level, and at its rising edge, the D flip-flop 65 is clocked and the state of the terminal g is read. At this time, since the terminal gll-j is kept at a high level, the state of the D71J block flop 65 changes, and the terminal i becomes a high level.

Therefore, relays 66A, 66B are driven, and second-stage layer width circuits 24A, 24B are connected to first-stage layer width circuits 23A, 23B, respectively. Light. The user knows that the sensitivity has been switched by this lighting and then injects the sample solution again.

(3) Detection type lol! , 37 has significantly deteriorated and become unusable and requires replacement (see (3) in Figure 5). By changing the sensitivity in (2), the state changes to ( in Figure 5).
1), but as the deterioration progresses, it becomes (2) in FIG. 5, and then reaches (3) in FIG.

The voltage at terminal a is at time t. When the reference voltage vref is exceeded, the terminal d becomes high level, the peak bold circuit 55 is reset, the terminal e becomes low level, and the terminal f becomes high level. Immediately after reset, the voltage at terminal C rises to the same level as the voltage at terminal a, but it reaches its peak at a voltage lower than the reference voltage vL and maintains that voltage, so the states of terminals e and f do not change, and the terminal g remains at low level.

The voltage at terminal a decreases, and at time t, the reference voltage v
When the voltage drops below ref, the terminal d becomes low level, and the terminal 2 becomes high level. At the rising edge, the state of terminal g, that is, the low level, is read into the D flip-flop 65, so the terminal i becomes low level, and the relay 66A,
66B is demagnetized, and the second stage layer width circuits 24A, 24B
is separated. Also, only the LBD 44° does not light up, but in this case, as described above, the LBD 44f lights up to instruct the user to replace the detection electrodes 37 and 38.

Next, a specific circuit for the replacement time detection unit 75 for lighting the LED 44f i is shown in FIG. 6 as a second embodiment, and its time chart is shown in FIG. 7. In addition, the arrangement of the replacement time detection section 75 is shown by a chain line in FIGS. 1 and 2.

A peak hold circuit 76 and a fourth comparator 77 are connected to the output terminal a of the first stage layer width circuit 23A for the analyte detection current. The peak hold circuit 76 is an operational amplifier 78. Diode 79° Reset transistor 80. Constant voltage power supply capacitor 81. It is composed of a field effect transistor 82 and the like. A fifth comparator 83 is connected to the output terminal k of the peak hold circuit 76.

The reference voltage □ of the fifth comparator 83 is set to a level higher than the voltage level at which the analyte detection electrode 37 deteriorates and needs to be replaced.

Output terminal 1 of the fifth comparator 83 is D 71 tube 7
0 tube 84, and its output terminal n is an LED 4 for instructing the replacement of the IT poles 37 and 38 for detecting test substances and interfering substances.
It is connected to the base of the 4f operating transistor 85 in a reverse bias state.

The output terminal j of the front E M 4 tv comparator 77 is connected to the NOT circuit 86, and the output terminal m of the NOT circuit 86 is connected to the NOT circuit 86.
The I'iD flip 7D7 is connected to the clock input terminal of the flip 84. The output terminal j of this comparator 77
is connected to a differentiating circuit 89 consisting of a capacitor 87 and a resistor 88, which is connected to the base of the reset transistor 800. This comparator 77 is for detecting when the sample solution starts flowing and when all the sample solution has finished flowing, and its reference voltage Vr
efl is set almost to the ground (GND) level, so that even if the detection electrode 37 deteriorates and the generated voltage becomes considerably low, the comparator 77 always operates. From the above, the magnitude relationship of each reference voltage is Vrefl
It is 〈■L□.

Next, the operation will be explained.

(1) When the detection electrode 37 is normal (see (1) in Fig. 7) When the sample solution flows in, the voltage at the output terminal a of the first stage layer width circuit 23A increases, and this becomes higher than the reference voltage Vrof□. Then, the output terminal J of the fourth comparator 77 becomes high level, and the reset transistor 80 is momentarily turned on via the differentiating circuit 89, and the capacitor 81 is discharged. Immediately after that, however, the light shielding is started again and the voltage at the output terminal of the peak hold circuit 76 rises to the same level as the voltage at the output terminal a (times T-T2).

At the peak hall voltage T□, the voltage at the output terminal l of the fifth comparator 83 changes from low level to high level.

The voltage at the terminal is determined by the fifth comparator 8 at time T2.
3, the voltage at the output terminal 107 of the comparator 83 becomes low level.

Further, the voltage at the terminal increases and reaches a peak at time T3.

After time T3, the voltage at terminal a decreases, but the voltage at terminal a is maintained at the peak voltage (〉vL,), so terminal 1
The state remains unchanged and remains at low level. Then, when the voltage at the terminal a falls below the level voltage ■ref, the voltage at the terminal j goes low and goes to a high level, and the voltage at the terminal m goes to high level, and at the rising edge, the voltage at the D flip 7 is set to 84. is clocked to read the state of terminal l, but at this time, since terminal 1 is at low level, the state of D7 lip-flop 84 does not change, and the voltage at terminal n remains at high level. Therefore, transistor 85 will not conduct and IJo 44f will not light up.

(2) When the detection electrode 37 has deteriorated significantly and cannot be used and needs to be replaced (see (2) in FIG. 7) The voltage at the terminal a reaches the reference voltage ■ at time T5. 1, the peak hold circuit 76 is reset during a running period in which the terminal j becomes a high level, and the terminal 1 becomes a high level. Immediately after resetting, the voltage at the terminal rises to the same level as the voltage at terminal a, but at time T6 it reaches a peak at a voltage lower than the reference voltage ■1□, and in order to maintain that voltage, terminal 1
The state S does not change and remains at a high level.

When the voltage at terminal a decreases and becomes lower than □ at the reference pressure Vre at time T, terminal i becomes low level and terminal m becomes high level, and at its rising edge, the state of terminal l, that is, high level, is D-flip. Since the signal is read into the seventh knob 84, the terminal n becomes low level, the reverse bias applied to the transistors 85 is released, the transistor 85 becomes conductive, and the LD switch instructs to replace the detection electrodes 37 and 38.
4f lights up.

The present invention also includes an embodiment in which the two-stage sensitivity switching of the first embodiment is combined with the second embodiment.

In that case, the peak hold circuits 55 and 76
and the fourth comparator 56, 77, third: +
5-It is desirable that the fifth comparators 63 and 83 and the knot circuits 69 and 86 be used in common.

〔Effect of the invention〕

According to the blood component quantitative meter of the present invention, it is very convenient to accurately detect the deterioration state of the electrode for detecting a test substance and take appropriate measures such as increasing the sensitivity or displaying an instruction to replace the electrode. There is.

[Brief explanation of drawings]

Fig. 1 is a block diagram of the first embodiment of the present invention, Fig. 2 is an overall configuration diagram, Fig. 3 is a front view of the front panel, Fig. 4 is an electric circuit diagram, Fig. 5 is a time chart thereof, FIG. 6 is an electric circuit diagram of the second embodiment, and FIG. 7 is its time chart. 27... Arithmetic circuit (arithmetic unit), 28... Display unit, 3
6... Channel, 37... Test substance detection electrode, 38.
・・11t for interfering substance detection, Adoration, 44c, 44r・
...LED (alarm, response means), 46...inlet, 62,63.83...comparator (comparison means),
66A, 66B... Sensitivity switching relay (response means) Procedural amendment (shu) January 9, 1980 Patent Application No. 213731, filed in 1988 2, Name of the invention Blood component quantitative meter 3, Person making the amendment Relationship to the case Applicant 4, Agent 5, Date of amendment order Voluntary amendment 6, Subject of amendment (1) Specification page 8, line 7, page 9, line 9, 1O
On the 9th line of the page, the words "100%" are corrected to "only." (2) On page 8, line 9 of the specification, "0%" is corrected to "none." (3) On page 9, line 18 of the specification, the phrase "r100%" is corrected to "only."

Claims (4)

[Claims] (1) A channel through which the carrier liquid of the test substance flows, an injection port for the test substance into this channel, an electrode for detecting the test substance inserted into the channel downstream of the injection port, and interfering substances. a detection electrode, a calculation unit that corrects the output electricity amount of the analyte detection electrode based on the output electricity amount of the interfering substance detection electrode, a display unit for displaying the calculation result of the calculation unit, and a calculation unit that corrects the output electricity amount of the analyte detection electrode, Comparing means that compares the amount of electricity output from the detection N pole with a reference amount of electricity for detecting the state of deterioration of the electrode for detecting the analyte, and outputs a signal when the comparison results in a predetermined state of deterioration; A blood component quantitative meter comprising a response means for inputting the output signal from the comparison means and performing a predetermined deterioration countermeasure operation. (2) the reference quantity of electricity is set to an amount corresponding to a state in which the electrode for detecting the analyte is unusable;
The blood component quantitative meter according to claim (1), wherein the response means is configured as an alarm. (3) The reference amount of electricity is set to an amount corresponding to an intermediate state between a normal usage state and an unusable deteriorated state of the analyte detection electrode, and the response means is set to the analyte detection electrode. The blood component quantitative meter according to claim 1, wherein the blood component quantitative meter is configured to increase the amplification factor of the output electrical quantity. (4) The reference quantity of electricity is Wi':m for detecting the analyte.
The alarm is set to an amount corresponding to an intermediate state between a normal use state and an unusable deteriorated state, and the response means increases the amplification factor of the output electricity amount of the analyte detection electrode. Claim No. 1 (1) consisting of
Blood component quantitative meter described in ).