WO2003077761A1 - Analyseur de sang - Google Patents

Analyseur de sang Download PDF

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Publication number
WO2003077761A1
WO2003077761A1 PCT/JP2003/003247 JP0303247W WO03077761A1 WO 2003077761 A1 WO2003077761 A1 WO 2003077761A1 JP 0303247 W JP0303247 W JP 0303247W WO 03077761 A1 WO03077761 A1 WO 03077761A1
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WO
WIPO (PCT)
Prior art keywords
wavelength
hemoglobin
blood
blood analyzer
light
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Application number
PCT/JP2003/003247
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English (en)
Japanese (ja)
Inventor
Shunji Egawa
Original Assignee
Citizen Watch Co., Ltd.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
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Publication date
Application filed by Citizen Watch Co., Ltd. filed Critical Citizen Watch Co., Ltd.
Publication of WO2003077761A1 publication Critical patent/WO2003077761A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14546—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring analytes not otherwise provided for, e.g. ions, cytochromes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/6813—Specially adapted to be attached to a specific body part
    • A61B5/6825—Hand
    • A61B5/6826—Finger
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/683—Means for maintaining contact with the body
    • A61B5/6838—Clamps or clips
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2560/00—Constructional details of operational features of apparatus; Accessories for medical measuring apparatus
    • A61B2560/04—Constructional details of apparatus
    • A61B2560/0462—Apparatus with built-in sensors

Definitions

  • the present invention relates to a blood analyzer for non-invasively measuring a specific component in blood, particularly, hemoglobin in blood.
  • hemoglobin particularly hemoglobin A 1c in a state of being bound to blood glucose
  • Hemoglobin binds to glucose according to the glucose concentration in the blood. This is an irreversible reaction with a slow reaction time. Since the life span of red blood cells is about 120 days, hemoglobin A 1c reflects the average blood glucose level in the past month or two.
  • Methods for analyzing hemoglobin A1c include high performance liquid chromatography (HPLC) and immunoassay.
  • HPLC high performance liquid chromatography
  • immunoassay for example, as a commercially available hemoglobin Alc analyzer for the HP LC method, there is a Tosoh automatic glycohemoglobin analyzer HLC-723G7 (medical device license number 35BZ0019).
  • An ADAMS Master-DM-3310 medical device approval number 2100BZZ 00391 is an example of an immunoassay hemoglobin Alc analyzer.
  • hemoglobin A1c analyzers collect venous blood from patients and examine whole blood. Such a method of testing caused pain and discomfort to the patient during blood collection. In addition, since blood cannot be collected without doctors, nurses, and laboratory technicians, and because the equipment is large and expensive, it is used for medical examinations for diabetes and medical examinations in hospitals, etc. It could not be used easily. Further, as an apparatus for inspecting the blood components without blood sampling, analysis contents are different is Parusuokishime coater to measure oxygen saturation of arterial blood (hereinafter abbreviated as "Sp_ ⁇ 2".). An example of such a pulse oximeter is disclosed in Japanese Patent Publication No. 53-26437 as an optical blood measuring device.
  • This optical blood measurement According to the measurement device, the change in transmitted light due to the pulsation of the blood flow is measured in two wavelength bands of 630 nm and 900 nm, and the ratio of these two changes, that is, the ratio of the absorption coefficient, is determined. and calculates the Sp_ ⁇ 2 of arterial blood.
  • the component ratio of the two components of O carboxymethyl hemoglobin (H -0 2) the de O carboxymethyl hemoglobin (hereinafter abbreviated as "Hb”.) Measured at two wavelengths 630 nm and 900 nm It was done.
  • the pulse O carboxymethyl meters is for obtaining the component ratio of only 2 components of Hb-0 2 and Hb, the presence of local ports carboxymethyl hemoglobin combined with carbon monoxide (Hb-C ⁇ ) was ignored. This is because the presence of Hb-CO caused negligible errors in clinical settings, such as during and after surgery, in intensive care units, and during emergency transport.
  • Hb_CO the analysis target.
  • Figure 8 is a commercially available pulse O carboxymethyl meter one shows the results obtained indirectly to Mog Robin A 1 c from S p0 2.
  • the light source for this device is a light emitting diode with 660 ⁇ m and 940 nm.
  • the subjects of the measurement experiment were 5 diabetic patients and 22 normal subjects, a total of 27 cases. The total was categorized into 16 cases of non-smokers who did not smoke and 11 cases of smokers who smoked. did.
  • the Parusuokishime Isseki one display value S p0 2, in order to convert hemoglobin A 1 c corresponding value, and the processing of 100- S P_ ⁇ 2. For example, if Sp_ ⁇ 2 92%, hemoglobin A 1 c corresponding value is set to 8%.
  • the result of the measurement experiment was The number of cases (frequency) is shown.
  • hemoglobin A 1c equivalent was high only in diabetic patients and low in normal subjects. In the smoker group as well, diabetic patients showed high levels, but normal subjects showed high levels. Thus, in the case of a smoker, there is a risk that hemoglobin A 1c may be measured as a high value, and that a conventional pulse oximeter cannot accurately determine hemoglobin A 1c. It was revealed.
  • an object of the present invention is to provide a blood analyzer capable of non-invasively analyzing the concentration of glycated hemoglobin in blood used as various diagnostic and medical indicators. Disclosure of the invention
  • the blood analyzer of the present invention when measuring the concentration of a specific component from among blood components using light having a plurality of different wavelengths, measuring at least Darico's hemoglobin as the specific component. Specifically, it is characterized by measuring hemoglobin A1c.
  • the wavelength of at least one of the plurality of lights is set to a wavelength at which the absorbance ratio of dalicohaemoglobin is maximized.
  • a specific component in blood for example, glycohemoglobin can be measured by non-invasive method, and thus, the risk of infection due to blood collection can be eliminated.
  • the blood analyzer since the blood analyzer has a simple configuration and can be miniaturized, an inexpensive blood analyzer can be realized, and a patient can easily perform a test at home.
  • the blood analyzer of the present invention is characterized in that, in addition to the glycohemoglobin, oxyhemoglobin and carboxyhemoglobin are measured as the specific components.
  • the light of a plurality of different wavelengths is set to a wavelength near the maximum value of the absorbance ratio of carboxyhemoglobin and the maximum value of the absorbance ratio of oxyhemoglobin.
  • the molar extinction coefficient of the daricohemoglobin, the molar extinction coefficient of the oxyhemoglobin, and the molar extinction coefficient of the lipoxyhemoglobin are respectively k1, k2, and k3.
  • the first wavelength is set in a region of k3>kl> k2
  • the second wavelength is set to kl ⁇
  • the region is set in the region of k 3> k 2
  • the third wavelength is set in the region of k 1 k 2 k 3.
  • oxyhemoglobin and carboxyhemoglobin in addition to glycohemoglobin, oxyhemoglobin and carboxyhemoglobin can be directly measured in a non-invasive manner.
  • the measurement results are in a state in which carboxyhemoglobin is included in either dalicohemoglobin or oxyhemoglobin, so there is a point that accuracy is required.
  • the present invention does not cause such a problem.
  • the concentrations of glycohemoglobin, oxyhemoglobin, and lipoxyhemoglobin are measured based on the maximum value of the absorbance ratio and the wavelength near the maximum value of the absorbance ratio, so that accurate measurement can be performed.
  • the result can be obtained.
  • the wavelengths of ⁇ 3 are preferably wavelengths of 600 ⁇ : L000nm, and specifically, the first wavelength is a wavelength of 65 ⁇ 780nm, and the second wavelength is Preferably, the wavelength is between 600 and 600 nm, and the third wavelength is between 850 and 00 nm.
  • glycohemoglobin is sometimes is sometimes used to agree to hemoglobin A le (H b A lc - ⁇ 2), to be precise, in particular hemoglobin having a glycated hemoglobin caries Chino specific chemical structure A 1 c.
  • Many types of glycohemoglobin are known in addition to hemoglobin A1'c.
  • the present invention can be used not only for analysis of hemoglobin A1c but also for other types of analysis of glycohemoglobin. Therefore, in this specification, the term "glycated hemoglobin" refers to a broad concept including hemoglobin Alc as well as other types.
  • FIG. 1 is an external view of a blood analyzer according to an embodiment of the present invention, wherein (a) is a front view and (b) is a side view.
  • FIG. 2 is a mounting view of the blood analyzer according to the embodiment of the present invention.
  • FIG. 3 is a cross-sectional view showing a sensor unit structure of the blood analyzer according to the embodiment of the present invention.
  • FIG. 4 is a block diagram of the blood analyzer according to the embodiment of the present invention.
  • Figure 5 is hemoglobin A le (H b A lc- 0 2), O carboxymethyl hemoglobin (H b - 0 2), absorbance showing the change of the molar extinction coefficient at the wavelength of the local port carboxymethyl hemoglobin (H b-CO) It is a characteristic curve.
  • FIG. 7 is an external view of a blood analyzer according to another embodiment of the present invention.
  • FIG. 8 shows the results of measurements performed using a conventional pulse oximeter.
  • This blood analyzer is a blood analyzer for examining the proportions of various hemoglobins contained in red blood cells in blood.
  • the blood analyzer 10 is provided with an insertion hole 11 for inserting a measurement site on a side surface, and has a substantially cylindrical shape so that a subject's finger can be inserted.
  • a switch 12 for turning on the power and starting an analysis and a display 13 for displaying an analysis result are provided on the front.
  • the display 13 displays hemoglobin Ale, which is an indicator of blood sugar control.
  • the third finger (middle finger) of the right hand into the insertion hole 11 and support the blood analyzer 10 lightly with the second finger (index finger) and fourth finger (ring finger) on both sides. Turn your palm up.
  • the living tissue 1 to be measured is the third finger of the right hand.
  • switch 12 is pressed with another finger, for example, the first finger (thumb) in this position, the power is turned on and the analysis is started.
  • the analysis result can be easily read because the display 13 is facing upward.
  • the living tissue 1 to be inserted into the insertion hole 11 is the third finger of the right hand, but the present invention is not limited to this finger, and other fingers can be similarly measured. In addition, all fingers and toes can be measured.
  • the shape of the insertion hole 11 of the blood analyzer it is possible to measure the hemoglobin A 1c with the earlobe or nose as a measurement target.
  • the insertion hole 11 is formed by a substantially cylindrical holder 27 having a closed end.
  • the living tissue 1, which is a finger, is inserted into the tip of the holder 27 so as to abut it.
  • the holder 27 is provided with a light receiving filter 26 at a portion where a finger pad touches, and a diffusion plate 25 is provided on the opposite side of the light receiving filter 26.
  • the diffusion plate 25 is formed by molding a transparent polystyrene (PS) resin or an acrylic (PMMA) resin. Light emitting elements 21, 22, and 23 are arranged close to the outside of the diffusion plate 25.
  • the light-emitting elements 21, 22, and 23 are chip-type light-emitting diodes having peak emission wavelengths of ⁇ 1, ⁇ 2, and ⁇ 3, respectively. Light-emitting elements 21, 22, and 23 are arranged close to each other, but cannot emit light from the same position. Therefore, a diffusion plate 25 is provided in order to minimize an error caused by a difference in the position of the light emitting elements 21, 22, 23. By providing the diffusion plate 25, the point light emitted by the chip-type light emitting diode is converted into the surface light emitted by the diffusion plate 25, and the effect of the light path difference between the light emitting elements 21, 22, and 23 is eliminated. .
  • the light emitting elements 21, 22, and 23 are light emitting diodes, but laser diodes having excellent wavelength selectivity may be used.
  • the light receiving filter 26 receives only the light transmitted through the living tissue 1 from the light of the wavelengths ⁇ 1, ⁇ 2, and ⁇ 3 respectively emitted from the light emitting elements 21, 22, and 23. That is, the light receiving filter 26 is an optical filter for attenuating fluorescent lights and sunlight, and reduces the influence of extraneous light leaking from the gap between the input hole 11 and the living tissue 1. In addition, the light receiving filter 26 also has a dustproof effect, so that cleaning can be easily performed.
  • the light receiving element 24 is disposed outside the light receiving filter 26.
  • the light receiving element 24 is a photodiode that receives light having wavelengths of ⁇ 1, ⁇ 2, and ⁇ 3.
  • the circuit board 30 mounts the light receiving element 24 and also mounts each unit (not shown) such as an arithmetic unit described later.
  • the calculation means obtains a change in photocurrent due to pulsation at each wavelength, and further calculates hemoglobin A1c. Its calculation The result is displayed by the display 13 connected to the circuit board 30.
  • a block diagram of the blood analyzer of this embodiment will be described with reference to FIG.
  • Light from these light emitting elements 21, 22, and 23 is applied to the finger as the living tissue 1.
  • the irradiated light is absorbed by various hemoglobins of the living tissue 1, but is also scattered by red blood cells.
  • the transmitted light is received by the light receiving elements 24 arranged facing each other with the living tissue 1 interposed therebetween.
  • the emission wavelengths ⁇ , ⁇ 2, and ⁇ 3 are in a relationship of ⁇ 1 and ⁇ 2 ⁇ 3, and are set to, for example, 630 nm, 680 nm, and 940 nm, respectively.
  • the light receiving element 24 receives the light emitted from the light emitting elements 21, 22, and 23, which is attenuated by passing through the living tissue 1 to have transmitted light amounts I1, 12, and I3.
  • the amplifier 32 converts the photocurrent of the light receiving element 24 into a voltage, and amplifies the voltage.
  • the transmitted light amounts I1, 12, and I3 at each wavelength include a pulsation component corresponding to a pulsation.
  • the output signal of the amplifier 32 is divided for each of the wavelengths ⁇ , ⁇ 2, and ⁇ 3, and supplied to the band-pass filters (BPF) 34, 35, and 36.
  • the BPFs 34, 35, and 36 remove high-frequency noise components contained in each signal, and further reduce the pulsating components of transmitted light at the respective wavelengths ⁇ 1, ⁇ 2, ⁇ 3 in the biological tissue 1. It outputs a corresponding amplitude signal, that is, a finger plethysmogram.
  • the pulsation extraction means (DET) 37, 38, 39 detects and extracts a signal corresponding to the amplitude value of the pulsation component of living tissue 1 for each wavelength from each output signal from the BPFs 34, 35, 36 ing. These detection signals correspond to the pulsatile components ⁇ 1, ⁇ 2, and ⁇ 3 of the transmitted light at the respective wavelengths; 1, ⁇ • 2, ⁇ 3 in the biological tissue 1, and are analog / digital converted data. .
  • the output signals ⁇ , ⁇ 2, ⁇ 3 of the DETs 37, 38, 39 are supplied to the calculating means 40, and the component ratios of various hemoglobins to all hemoglobins are calculated. Then, the display means 41 displays the component ratio of hemoglobin A 1c as the calculation result.
  • the calculation of the hemoglobin component ratio calculated by the calculating means 40 will be described. From the molar extinction coefficient of various hemoglobins and the absorbance of the living tissue 1, the component ratio of various hemoglobins, which are absorption components, is calculated by mathematical conversion.
  • X is HbAl c- ⁇ 2
  • y is Hb-0
  • z is the concentration (concentration in unit volume) of the Hb-CO.
  • k is a proportional constant representing the optical path length due to the blood vessel.
  • the absorbance by the biological tissue 1 at the wavelength 1 (i 1, 2, 3), the absorbing component mainly HbA 1 c- ⁇ 2, due to various hemoglobin Hb-0 2, H b-CO is there.
  • the component ratio X of HbA 1 c—O 2 is the ratio of the concentration of Hb A 1 c— ⁇ 2 to the concentration of total hemoglobin, and is given by equation (8).
  • ⁇ u has been described as a molar extinction coefficient, but if the concentrations of various hemoglobins are unknown, they can be treated as absorbance under the same concentration conditions. At this time, the dimensions change, but the basic idea is the same.
  • the absorption spectrum used in the absorption analysis will be described.
  • the electron spectrum derived from the electronic transition has a large absorption spectrum in the ultraviolet-visible region.
  • the vibration spectrum derived from molecular vibration has an absorption spectrum in the near infrared region, but the absorption itself is small.
  • analysis is difficult because the absorption by hemoglobin is small and the absorption by water molecules is large.
  • the emission wavelengths 1 ⁇ 2 and ⁇ 3 are visible from 600 nm to 1000 nm. Set from light and near-infrared light. Furthermore, when setting the emission wavelength by focusing on the difference in molar extinction coefficient, it is advisable to set it from the visible light region where the electronic spectrum appears, that is, from 600 nm to 780 nm.
  • FIG. 5 shows the measured P and light characteristic curves.
  • FIG. 6 shows the characteristic curves in which the ratio of the molar extinction coefficient of each type of hemoglobin is P and the light intensity ratio.
  • the vertical axis is the molar extinction coefficient of each hemoglobin component, and the horizontal axis is the wavelength.
  • the first k 1 molar extinction coefficient of HbAl c- 0 2 is a component
  • the molar extinction coefficient k 2 of the Hb-0 2 which is the second component is the third component Hb- C_ ⁇ molar absorption Let the coefficient be k3.
  • the first wavelength ⁇ ⁇ a wavelength having a large difference in molar extinction coefficient between various hemoglobins is selected.
  • FIG. 5 there is a large difference in the molar extinction coefficient near the wavelength of 630 nm.
  • Hb -CO, HbAl c- ⁇ 2, Hb_ ⁇ 2 that is, a k 3> k 1> k 2 .
  • the first wavelength ⁇ 1 is set from the range from 600 nm to 650 nm.
  • the emission wavelength ⁇ 1 is designed to be 63 O nm and an orange light-emitting diode is used, it is advantageous in terms of cost and delivery time in parts procurement.
  • the second wavelength ⁇ 2 is set from a region different from the molar extinction coefficient ratio at the previously set wavelength ⁇ 1. According to FIG. 5, in the region from 650 nm to 780 nm, when the molar extinction coefficient is arranged in descending order, HbAl c—O 2 , Hb—CO, Hb—O 2 , and HbAl c—O 2 and Hb—CO It turns out that it is reversed. That is, kl ⁇ k3> k2.
  • the second wavelength ⁇ 2 is set from the range of 650 nm to 780 nm.
  • the emission wavelength ⁇ 2 is 680 nm and a red emission diode is used, it is advantageous in terms of cost and delivery time in parts procurement.
  • This isosbestic characteristic shows a characteristic different from the ratio of the molar extinction coefficient at the wavelengths ⁇ and ⁇ 2.
  • the third wavelength ⁇ 3 is set from the range of 850 nm to 1000 nm. For example, if a design is made to use a 940 nm infrared light emitting diode, which is often used for optical communication using infrared light with an emission wavelength of ⁇ 3, it is advantageous in terms of cost and delivery time in parts procurement.
  • the component ratio of hemoglobin can be accurately calculated.
  • the wavelength of the light-emitting diode from the light-emitting diodes having a large supply amount, it is possible to design a more easily procured and inexpensive product.
  • an optical analyzer can reduce the error when measured at an absorption band (singular point) peculiar to a substance.
  • HbAl c- 0 2 shown in FIG. 5 the wavelength one molar extinction coefficient graph Hb-CO, and HbAl c- ⁇ 2 curve arrows and Moriaga One in which point (position of the wavelength ⁇ ⁇ ), Hb — The point where the CO curve rises slightly (the wavelength ⁇ 2 position) is the singular point.
  • HbAl c- ⁇ 2 Hb-wavelength of CO - difficult to find the singular point in the molar extinction coefficient graphs.
  • the present invention is, HbA 1 c- 0 2 shown in FIG. 6, Hb-0 2, Hb-CO based on the wavelength one molar absorbance ratio, locate the wavelength of the absorbance ratio is maximum, measurement results definitive in this wavelength From the analysis.
  • the method of setting the wavelengths ⁇ 1, ⁇ 2, ⁇ 3 having the maximum absorbance ratio is a method of obtaining the ratio of the molar extinction coefficient of various hemoglobins, that is, the absorbance ratio.
  • the absorbance ratio on the vertical axis in FIG. 6 is the ratio of the molar extinction coefficient of various hemoglobins, kj / (k1 + k2 + k3).
  • the horizontal axis is the wavelength.
  • the P and luminous intensity ratio are k 3 / (k 1 + k 2 + k 3).
  • the maximum of the absorbance ratio of Hb—CO is in the wavelength range from 600 nm to 650 nm. Therefore, the first wavelength 1 may be set from this wavelength region. In particular, it can be seen that it is almost maximum around 630 nm. This is because the absorption band of Hb—CO is in this region.
  • the maximum of the absorbance ratio of HbAl C_ ⁇ 2 it can be seen that from wavelength 650 nm to 780 nm region. Therefore, the second wavelength ⁇ 2 may be set from this wavelength region. In particular, it can be seen that it is almost maximum around 680 nm. This is because there is an absorption band of Hb A 1 c— ⁇ 2 in this region.
  • the third wavelength ⁇ 3 is set from this region.
  • the wavelengths ⁇ , ⁇ 2, and ⁇ 3 are set from the wavelengths at which the absorbance ratio of various hemoglobins is maximum or the absorbance ratio is maximum.
  • the maximum of the absorbance ratio may be obtained from the absorbance obtained by an experiment.
  • the calculation can be simplified by selecting the isosbestic point for the emission wavelength.
  • the third wavelength is already choose isosbestic point
  • the second wavelength may be chosen isosbestic point of the near with 650 nm HbAl c- ⁇ 2 and Hb-CO.
  • the equation (11) is obtained, and the calculation can be simplified.
  • ⁇ 3 1 ( £ 22 8 33 ⁇ ⁇ 21 £ 32) + a 2 ( £ 11 ⁇ 32— ⁇ 11 £ 33 / + a 3 ( £ 11 £ 23— £ 11 £ 22)
  • a mass percent concentration such as a component ratio (%) of various hemoglobins in blood and a substance amount in a fixed volume such as an average blood sugar level (mg / d1) are determined. be able to.
  • both the component ratio and the blood glucose level can be displayed on the display unit of the blood analyzer, and in some cases, only the average blood glucose level can be displayed.
  • FIG. 7 is an external view of a blood analyzer according to another embodiment of the present invention. The difference between the blood analyzer of this embodiment and the blood analyzer shown in FIG.
  • Hb—CO carboxyhemoglobin
  • Hb—CO often binds to the carbon monoxide contained in tobacco smoke and can be used as an indicator of smoker health care.
  • Hb_C ⁇ can also be a cause of shortness of breath, and is therefore an important indicator of health care.
  • the non-invasive and inexpensive blood analyzer according to the present invention is a useful self-care means that not only can perform measurement without pain but also can improve treatment consciousness for diabetic patients. And it can prevent complications such as neuropathy, retinopathy and nephropathy. Furthermore, if the self-measurement of glycated hemoglobin is measured not only for diabetic patients but also for healthy adults, it will help prevent diabetes.

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Abstract

La présente invention concerne un analyseur de sang servant à mesurer les concentrations d'hémoglobine sanguine qui constituent des indicateurs pour le diagnostic d'un diabète ou la surveillance du taux de glycémie. Il s'agit de sélectionner, à partir des courbes caractéristiques montrant les rapports de coefficient d'absorption molaire de trois composants de l'hémoglobine comprenant HbAlc-O2, Hb-O2 et Hb-CO, la longueur d'onde à laquelle le taux d'absorbance de chaque composant atteint une pointe ou la longueur d'onde à laquelle le taux d'absorbance de chaque composant atteint le niveau maximum. Ensuite, le rapport de composition des composants de l'hémoglobine est calculé sur la base des coefficients d'absorption molaire des composants de l'hémoglobine à ces longueurs d'onde et des absorbances d'un tissu biologique à ces longueurs d'onde. Les concentrations des composants de l'hémoglobine sont ainsi indiquées de manière non invasive.
PCT/JP2003/003247 2002-03-18 2003-03-18 Analyseur de sang WO2003077761A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
JP2002073675A JP2005253478A (ja) 2002-03-18 2002-03-18 ヘモグロビン分析装置
JP2002-073675 2002-03-18

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Cited By (13)

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EP2476369A1 (fr) * 2007-03-27 2012-07-18 Masimo Laboratories, Inc. Capteur optique à longueurs d'onde multiples
WO2013104629A1 (fr) * 2012-01-13 2013-07-18 Kaptalia Monitoring Oxymètre
US8965471B2 (en) 2007-04-21 2015-02-24 Cercacor Laboratories, Inc. Tissue profile wellness monitor
US9167995B2 (en) 2005-03-01 2015-10-27 Cercacor Laboratories, Inc. Physiological parameter confidence measure
CN105748089A (zh) * 2016-02-01 2016-07-13 刘进 一种氧供参数监测方法及监测装置
TWI555504B (zh) * 2014-06-06 2016-11-01 國立交通大學 血液脈波內生特徵分割系統與方法
US9839381B1 (en) 2009-11-24 2017-12-12 Cercacor Laboratories, Inc. Physiological measurement system with automatic wavelength adjustment
WO2019138374A1 (fr) * 2018-01-09 2019-07-18 Medtronic Monitoring, Inc. Système et procédé de surveillance non invasive de produits finaux de glycation avancée (age)
US10729402B2 (en) 2009-12-04 2020-08-04 Masimo Corporation Calibration for multi-stage physiological monitors
US11039768B2 (en) 2018-01-09 2021-06-22 Medtronic Monitoring, Inc. System and method for non-invasive monitoring of hemoglobin
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