Photoelectric detection system and method for hemoglobin detection

Abstract

The invention relates to a photoelectric detection system and method for hemoglobin detection, and relates to the technical field of spectral analysis and biomedical engineering. The method mainly comprises the following steps: controlling a light source module in the buckle type shell structure to emit light with different wavelengths, and enabling the light to penetrate through a blood transfusion tube and blood placed in the buckle type shell structure; a photoelectric detector module in the buckle type shell structure is controlled to obtain the blood transmission light intensity of the multi-wavelength light to the blood transfusion tube; calculating basic absorbance corresponding to the first wavelength and the second wavelength by using a hemoglobin absorption model, and correcting the basic absorbance by using a correction model to obtain final absorbance; according to the final absorbance corresponding to the first wavelength and the final absorbance corresponding to the second wavelength and the effective optical path length, predicting the concentration of deoxyhemoglobin and the concentration of oxyhemoglobin; and adding the deoxyhemoglobin concentration and the oxyhemoglobin concentration to obtain the total hemoglobin concentration.

Description

Technical Field

[0001] This invention relates to the fields of spectral analysis technology and biomedical engineering, and in particular to a photoelectric detection system and method for hemoglobin detection. Background Technology

[0002] In current clinical practice, hemoglobin concentration is a crucial indicator for determining whether a patient requires a blood transfusion, typically measured by drawing a blood sample and using a blood gas analyzer. Although the testing time can be controlled within 2 minutes, this method still has the following problems: Continuous real-time monitoring is not possible, making it difficult to reflect dynamic changes in blood status during surgery in a timely manner; blood drawing and processing require specialized skills, which are time-consuming and labor-intensive; blood analyzers in the laboratory are bulky and cannot be integrated into small catheter-type instruments; some non-contact optical detection devices (such as finger-clip pulse oximeters) lack sufficient sensitivity, have poor anti-interference capabilities, and cannot cope with complex scenarios and detection needs in intraoperative clinical settings. Although some finger-clip and wristband spectrometers can be used for surface monitoring, they are not suitable for use in in vivo pathways or transducer sites. Summary of the Invention

[0003] The present invention aims to provide a photoelectric detection system and method for hemoglobin detection, so as to overcome the shortcomings of the prior art. The technical problem to be solved by the present invention is achieved through the following technical solution.

[0004] This invention provides a photoelectric detection system for hemoglobin detection. The photoelectric detection system includes: a photoelectric detection device and a hemoglobin detection processor connected to each other. The photoelectric detection device has a snap-fit ​​housing structure and includes: a light source module and a photodetector module. The hemoglobin detection processor is used for the following steps: The light source module inside the snap-fit ​​housing structure is controlled to emit multi-wavelength light, which penetrates the blood transfusion tube placed inside the snap-fit ​​housing structure; the multi-wavelength light includes at least a first wavelength light and a second wavelength light; The photodetector module inside the snap-fit ​​housing structure is controlled to obtain the intensity of the multi-wavelength light transmitted through the blood in the transfusion vessel. Calculate the basic absorbance corresponding to the first wavelength light and the second wavelength light respectively, and correct the basic absorbance to obtain the final absorbance; The concentrations of deoxyhemoglobin and oxyhemoglobin are determined by the final absorbance and effective optical path length corresponding to the first wavelength light and the second wavelength light, respectively. The total hemoglobin concentration is obtained by adding the concentrations of deoxyhemoglobin and oxyhemoglobin.

[0005] In an optional embodiment, calculating the basic absorbance corresponding to the first wavelength light and the second wavelength light respectively includes: The basic absorbance of the first wavelength light is calculated based on the blood transmission light intensity and the reference light intensity of physiological saline. The basic absorbance of the second wavelength light is calculated based on the blood transmission light intensity and the reference light intensity of physiological saline.

[0006] In an optional embodiment, correcting the baseline absorbance to obtain the final absorbance includes: Determine whether the light absorption compensation condition is met; If the light absorption compensation condition is met, then perform light absorption compensation and proceed to the step of determining whether the turbidity compensation condition is met before continuing execution. If the light absorption compensation condition is not met, determine whether the turbidity compensation condition is met. If the turbidity compensation condition is met, then perform turbidity compensation and proceed to the step of determining whether the flow field compensation condition is met to continue execution. If the turbidity compensation condition is not met, determine whether the flow field compensation condition is met. If the flow field compensation conditions are met, flow field compensation is performed, and the process jumps to the step of determining whether the temperature compensation conditions are met to continue execution. If the flow field compensation condition is not met, determine whether the temperature compensation condition is met. If the temperature compensation conditions are met, temperature compensation is performed to obtain the final absorbance.

[0007] In an optional embodiment, the light absorption compensation process is as follows: The ratio of total light intensity to the reference value of the clean pipe wall is calculated by measuring the light intensity values ​​from multiple angles and directions. Compensation is achieved by multiplying the base absorbance by the ratio.

[0008] In an optional embodiment, the turbidity compensation process is as follows: The photodetector module obtains the light intensity of the third wavelength light at the center position and the light intensity at the preset angle position in the light source module. Calculate forward scattering data based on the light intensity at the center position and the light intensity at the preset angle position; Calculate the product of the forward scattering data and the interference coefficient of turbidity at the third wavelength; Turbidity compensation is performed using the difference between the base absorbance and the product.

[0009] In an optional embodiment, the flow field compensation process is as follows: The photodetector module obtains the light intensity of the first wavelength light and the second wavelength light in the light source module at the center position and the light intensity at the preset angle position, respectively. Calculate the asymmetry of the first wavelength light based on the light intensity at the center position and the light intensity at the preset angle position; calculate the asymmetry of the second wavelength light based on the light intensity at the center position and the light intensity at the preset angle position. Flow field compensation is performed using the asymmetry corresponding to the first wavelength light and the asymmetry corresponding to the second wavelength light.

[0010] In an optional embodiment, the flow field compensation based on the asymmetry corresponding to the first wavelength light and the asymmetry corresponding to the second wavelength light includes: Calculate the absolute value of the difference between the asymmetry corresponding to the first wavelength light and the asymmetry corresponding to the second wavelength light; Flow field compensation is performed based on the absolute value of the difference and the eddy current compensation coefficient.

[0011] In an optional embodiment, the temperature compensation process is as follows: Obtain the real-time temperature and calibration temperature at the current moment; Temperature compensation is performed based on the real-time temperature and the calibrated temperature.

[0012] In an optional embodiment, determining the deoxyhemoglobin concentration and oxyhemoglobin concentration using the final absorbance and effective optical path length corresponding to the first wavelength light and the second wavelength light, respectively, includes: The absorbance vector is determined based on the final absorbance corresponding to the first wavelength light and the second wavelength light, respectively. The concentrations of deoxyhemoglobin and oxyhemoglobin are determined by the absorbance vector, the absorbance coefficient matrix, and the effective optical path length.

[0013] This invention provides a photoelectric detection method for hemoglobin detection, wherein the method is applied to a hemoglobin detection processor in a photoelectric detection system for hemoglobin detection, and the method includes: The light source module inside the snap-fit ​​housing structure is controlled to emit multi-wavelength light, which penetrates the blood transfusion tube placed inside the snap-fit ​​housing structure; the multi-wavelength light includes at least a first wavelength light and a second wavelength light; The photodetector module inside the snap-fit ​​housing structure is controlled to obtain the intensity of the multi-wavelength light transmitted through the blood in the transfusion vessel. Calculate the basic absorbance corresponding to the first wavelength light and the second wavelength light respectively, and correct the basic absorbance to obtain the final absorbance; The concentrations of deoxyhemoglobin and oxyhemoglobin are determined by the final absorbance and effective optical path length corresponding to the first wavelength light and the second wavelength light, respectively. The total hemoglobin concentration is obtained by adding the concentrations of deoxyhemoglobin and oxyhemoglobin. Embodiments of the present invention offer the following advantages: This invention provides a photoelectric detection system and method for hemoglobin detection. The photoelectric detection system includes an interconnected photoelectric detection device and a hemoglobin detection processor. The photoelectric detection device has a snap-fit ​​housing structure and includes a light source module and a photodetector module. The hemoglobin detection processor is used for the following steps: controlling the light source module inside the snap-fit ​​housing structure to emit multi-wavelength light, so that the multi-wavelength light penetrates a transfusion tube placed inside the snap-fit ​​housing structure; the multi-wavelength light includes at least a first wavelength light and a second wavelength light; controlling the photodetector module inside the snap-fit ​​housing structure to acquire the light intensity transmitted through the blood in the transfusion tube by the multi-wavelength light; calculating the basic absorbance corresponding to the first wavelength light and the second wavelength light respectively, and correcting the basic absorbance to obtain the final absorbance; determining the deoxyhemoglobin concentration and oxyhemoglobin concentration by the final absorbance corresponding to the first wavelength light and the second wavelength light respectively and the effective optical path length; and adding the deoxyhemoglobin concentration and the oxyhemoglobin concentration to obtain the total hemoglobin concentration. The snap-fit ​​shell structure in this application fits the transparent transfusion vessel, avoiding multi-layer interference in the optical path. Based on the intensity of blood transmitted through the transfusion vessel by multiple wavelengths of light, dynamic monitoring of changes in hemoglobin concentration can be achieved, providing assistance for intraoperative transfusion judgment. Attached Figure Description

[0014] Figure 1 This is a structural diagram of a photoelectric detection device provided in an embodiment of the present invention; Figure 2 This is a flowchart of a photoelectric detection method for hemoglobin detection provided in an embodiment of the present invention; Figure 3 This is a flowchart of a basic absorbance correction method provided in an embodiment of the present invention; Figure 4 This is a schematic diagram of the structure of a hemoglobin detection processor provided in an embodiment of the present invention. Detailed Implementation

[0015] It should be noted that, unless otherwise specified, the embodiments and features described in this application can be combined with each other. The present invention will now be described in detail with reference to the accompanying drawings and embodiments.

[0016] This invention provides a photoelectric detection system for hemoglobin detection, comprising: a photoelectric detection device and a hemoglobin detection processor connected to each other. Please refer to... Figure 1This embodiment provides a photoelectric detection device with a snap-fit ​​housing structure. One side opening allows it to be clamped to the outside of the transfusion tube. It has a limiting protrusion or groove to prevent slippage. Figure 1 The image shown is a photoelectric detection device provided in this embodiment. The photoelectric detection device includes: a light source module and a photodetector module. The light source module is disposed on one side of the housing and is used to emit directional light. The photodetector module is a high-sensitivity photodetector module disposed opposite to the light source module on the other side of the housing and is used to receive blood transmitted or scattered light.

[0017] In this embodiment, the photoelectric detection device module is detachable, disposable, or reusable. It can adapt to standard transfusion tube diameters ranging from approximately Φ2–5mm, or provide different models of detection components for different diameters. The photoelectric detection device internally includes an FPC or PCB circuit board for connecting the light source module, photodetector module, power supply, analog front-end, and signal output interface; a cable lead-out port connects to the hemoglobin detection processor. Additionally, the snap-fit ​​housing structure features a transparent housing window to enhance light throughput and stability.

[0018] like Figure 2 As shown, this embodiment provides a photoelectric detection method for hemoglobin detection. The hemoglobin detection processor is connected to and controls the photoelectric detection device, and then performs hemoglobin detection based on the data acquired by the photoelectric detection device. This detection method is applied to hemoglobin detection processing, that is, the hemoglobin detection processor is used in the following steps: S101, control the light source module inside the snap-fit ​​housing structure to emit multi-wavelength light, so that the multi-wavelength light penetrates the blood transfusion tube placed inside the snap-fit ​​housing structure.

[0019] The multi-wavelength light includes at least a first wavelength light and a second wavelength light. Specifically, the multi-wavelength light can be 415nm, 430nm, 540nm, 800nm, etc., but this embodiment does not specify a particular wavelength. Specifically, in this embodiment, the first wavelength light is 430nm, which corresponds to the strong characteristic absorption region of hemoglobin, and the second wavelength light is 540nm, which corresponds to the differential absorption region of oxytocin / deoxyhemoglobin.

[0020] like Figure 2 As shown, the internal circular structure of the photoelectric detection device for blood transfusion vessels is a component to prevent the blood transfusion vessels from being blocked. The blood transfusion vessels are placed behind the photoelectric detection device, and the light source module inside the snap-fit ​​housing structure is controlled to emit multi-wavelength light, so that the multi-wavelength light can penetrate the blood transfusion vessels placed inside the snap-fit ​​housing structure.

[0021] S102, control the photoelectric detector module inside the snap-fit ​​housing structure to obtain the blood transmission light intensity of the multi-wavelength light through the transfusion vessel.

[0022] S103, calculate the basic absorbance corresponding to the first wavelength light and the second wavelength light respectively, and correct the basic absorbance to obtain the final absorbance.

[0023] In one optional embodiment provided in this application, the calculation of the basic absorbance corresponding to the first wavelength light and the second wavelength light respectively includes: calculating the basic absorbance of the first wavelength light based on the blood transmission light intensity and the saline reference light intensity; and calculating the basic absorbance of the second wavelength light based on the blood transmission light intensity and the saline reference light intensity.

[0024] Specifically, in this embodiment, the basic absorbance corresponding to the first wavelength light and the second wavelength light can be calculated according to the following formulas:

[0025] in, Based on absorbance, The intensity of light transmitted through the blood (central detector). The reference light intensity for physiological saline (stored during initialization). This represents either the first wavelength of light or the second wavelength of light.

[0026] like Figure 3 As shown, in an optional embodiment provided in this application, correcting the base absorbance to obtain the final absorbance includes: S30, determine whether the light absorption compensation condition is met.

[0027] In this embodiment, the light absorption compensation condition can be: when the depolarization degree (DoLP) change is >0.05, when the frequency is increased to 1kHz when DoLP <0.7, or when it is forcibly triggered after each light source pulse.

[0028] S31. If the light absorption compensation condition is met, then light absorption compensation is performed.

[0029] In this embodiment, light absorption compensation is used to suppress stray light interference caused by reflections / scratches on the infusion tube wall, and to resolve systematic errors caused by tube wall contamination. After performing light absorption compensation, the process jumps to step S32 to determine whether the turbidity compensation conditions are met and continues execution.

[0030] Specifically, the light absorption compensation process is as follows: the total light intensity is calculated by using the light intensity values ​​from multiple angles; the real-time depolarization degree is calculated based on the light intensity and the linear polarization component; the ratio of the real-time depolarization degree to the clean pipe wall reference value is calculated; and polarization compensation is performed by multiplying the base absorbance and the ratio.

[0031] In this embodiment, the total light intensity can be calculated using the following formula:

[0032] in, Total light intensity , for, The light intensity value is the value in the 0° polarization direction. This represents the light intensity value in the 45° polarization direction. This represents the light intensity value in the 90° polarization direction.

[0033] Then, the real-time depolarization degree is calculated according to the following formula:

[0034] in, To achieve real-time depolarization, polarization compensation is then performed using the following formula:

[0035] in, Based on absorbance, This is a reference value for clean pipe walls (reference value for clean pipe walls ≈ 0.98).

[0036] S32. If the light absorption compensation condition is not met, determine whether the turbidity compensation condition is met.

[0037] In this embodiment, the turbidity compensation condition can be a sudden change in scattered light or the occurrence of an abnormal threshold. For example, a sudden change in scattered light can be a change in the intensity of scattered light after polarization compensation of >5%, and an abnormal threshold is when the absolute difference between scattered light and transmitted light is >20% of the transmitted light. This embodiment does not make specific limitations on this.

[0038] S33. If the turbidity compensation condition is met, then turbidity compensation is performed.

[0039] Turbidity compensation is used to eliminate light scattering interference caused by suspended particles (blood cells, lipid particles, etc.) in the blood, preventing false concentration misjudgments due to increased absorbance. After turbidity compensation, the process jumps to step S34 to determine whether the flow field compensation conditions are met before continuing execution.

[0040] Specifically, the turbidity compensation process is as follows: the light intensity of the third wavelength light at the center position and the light intensity at the preset angle position are obtained through the photodetector module; forward scattering data are calculated based on the light intensity at the center position and the light intensity at the preset angle position; the product of the forward scattering data and the interference coefficient of turbidity at the third wavelength light is calculated; and turbidity compensation is performed by the difference between the base absorbance and the product.

[0041] The wavelength of the third wavelength light can be 800nm, and the preset angle can be ±15°. In this embodiment, the forward scattering data can be calculated using the following formula:

[0042] in, Forward scattering data, The scattering coefficient (calibrated value ≈ 0.35 mL / mg) is... 15° off-axis detector with 800nm ​​light intensity For a -15° off-axis detector with 800nm ​​light intensity, The light intensity at the center of the detector at 800nm.

[0043] In this embodiment, it can be achieved through the formula Turbidity compensation is performed, among which Turbidity at wavelength The interference coefficient, Forward scattering data, Based on absorbance.

[0044] Turbidity compensation addresses light scattering interference caused by suspended particles (blood cells, lipid microparticles) in the blood. When light passes through turbid blood, these suspended particles cause some photons to change their path (Mie scattering), resulting in a false decrease in the intensity of transmitted light received by the detector. To address this issue, the compensation mechanism in this application monitors the proportion of scattered light at an 800nm ​​reference wavelength (where water absorption is lowest), subtracting the false absorbance increase caused by turbidity from the base absorbance. This leverages the insensitivity of the 800nm ​​wavelength to hemoglobin to achieve precise quantification of scattering interference.

[0045] S34. If the turbidity compensation condition is not met, determine whether the flow field compensation condition is met.

[0046] In this embodiment, the flow field compensation conditions can be: when the 800nm ​​signal pulsation frequency changes by more than 10% (indicating a change in flow velocity), when the spatial asymmetry AS is greater than 0.15 (indicating strong turbulence), and when a trigger flag is detected every 5ms, etc.

[0047] S35, if the flow field compensation conditions are met, then flow field compensation will be performed.

[0048] In this embodiment, flow field compensation is used to eliminate the uneven optical path distribution caused by blood flow turbulence / eddies and the measurement distortion caused by local aggregation of blood cells. After performing flow field compensation, the process jumps to step S36 to determine whether the temperature compensation condition is met and continues execution.

[0049] Specifically, the flow field compensation process is as follows: the photodetector module acquires the light intensity of the first wavelength light and the second wavelength light at the center position and the light intensity at the preset angle position, respectively; the asymmetry corresponding to the first wavelength light is calculated based on the light intensity of the first wavelength light at the center position and the light intensity at the preset angle position; the asymmetry corresponding to the second wavelength light is calculated based on the light intensity of the second wavelength light at the center position and the light intensity at the preset angle position; and flow field compensation is performed based on the asymmetry corresponding to the first wavelength light and the asymmetry corresponding to the second wavelength light.

[0050] The flow field compensation based on the asymmetry corresponding to the first wavelength light and the asymmetry corresponding to the second wavelength light includes: calculating the absolute value of the difference between the asymmetry corresponding to the first wavelength light and the asymmetry corresponding to the second wavelength light; and performing flow field compensation based on the absolute value of the difference and the eddy current compensation coefficient.

[0051] In this embodiment, flow field compensation can be performed using the following formula:

[0052]

[0053]

[0054] in, Based on absorbance, This represents the absorbance after flow field compensation. For left-biased detectors at wavelength Light intensity, For right-biased detectors at wavelength Light intensity. The asymmetry corresponds to the first wavelength of light. This represents the asymmetry corresponding to the second wavelength of light. This is the eddy current compensation coefficient.

[0055] In this embodiment, detectors with a left / right offset of 15° synchronously collect light intensity, and then calculate the asymmetry AS = |left light intensity - right light intensity| / average light intensity. After that, calculate the difference in AS between the two wavelengths (ΔAS = |AS415 - AS540|), where 415nm is sensitive to cell aggregation and 540nm is sensitive to oxygenation status. The absorbance reading is reduced proportionally according to the ΔAS value, and the compensation intensity is adaptively adjusted with the flow rate, utilizing the difference in response of hemoglobin to eddies.

[0056] S36. If the flow field compensation condition is not met, determine whether the temperature compensation condition is met.

[0057] In this embodiment, the temperature compensation conditions can be: when a temperature fluctuation > 0.5℃ is detected, or the system automatically executes once per second, or an emergency trigger is made when the temperature change rate > 1℃ / min, etc. This embodiment does not make specific limitations on these conditions.

[0058] S37. If the temperature compensation condition is met, temperature compensation is performed to obtain the final absorbance.

[0059] Specifically, temperature compensation corrects for hemoglobin spectral drift and detector response deviation caused by temperature changes, maintaining the stability of concentration measurements. The temperature compensation process involves: acquiring the real-time temperature and calibration temperature; and performing temperature compensation based on the real-time temperature and the calibration temperature.

[0060] This embodiment can be achieved through formulas. Temperature compensation is performed, among which The base absorbance is T0, which is 25℃ (calibration temperature), and T is the measured real-time temperature (tube wall temperature in °C).

[0061] In this embodiment, the tube wall temperature is monitored in real time by an embedded temperature sensor, and an exponential correction model is applied: for every 1°C increase in temperature, the 415nm signal is amplified by 1.5% (to offset absorption attenuation), while the detector gain is reverse-compensated (the gain decreases by 0.3% per °C), thus solving the defect of traditional solutions that only compensate for a single factor.

[0062] S104, the concentrations of deoxyhemoglobin and oxyhemoglobin are determined by the final absorbance and effective optical path length corresponding to the first wavelength light and the second wavelength light, respectively.

[0063] In one optional embodiment provided in this application, determining the deoxyhemoglobin concentration and oxyhemoglobin concentration by means of the final absorbance corresponding to the first wavelength light and the second wavelength light and the effective optical path length, respectively, includes: determining an absorbance vector based on the final absorbance corresponding to the first wavelength light and the second wavelength light; and solving for the deoxyhemoglobin concentration and oxyhemoglobin concentration by means of the absorbance vector, the absorption coefficient matrix and the effective optical path length.

[0064]

[0065] in, This represents the final absorbance corresponding to the first wavelength of light. These represent the final absorbance corresponding to the second wavelength of light. The absorption capacity of deoxyhemoglobin at 415 nm (1.25 × 10⁻⁶) 5 ), The absorption capacity of oxyhemoglobin at 415 nm (1.12 × 10⁻⁶) 5 ), The absorption capacity of deoxyhemoglobin at 540 nm (3.5 × 10⁻⁶) 4 ), The absorption capacity of oxyhemoglobin at 540 nm (1.4 × 10⁻⁶) 4 ), For effective optical path length, Let the concentration of deoxyhemoglobin be the solution. Let be the concentration of oxyhemoglobin to be determined.

[0066] In this embodiment, the effective optical path length is calculated using the following formula:

[0067] in, The refractive index of blood is approximately 1.36. Calculations based on 940nm photon time of flight For the speed of light (3×10) 10 (cm / s).

[0068] S105, the total hemoglobin concentration is obtained by adding the concentration of deoxyhemoglobin and the concentration of oxyhemoglobin.

[0069] Specifically, this embodiment uses the formula The total hemoglobin concentration was obtained.

[0070] This embodiment provides a photoelectric detection method for hemoglobin detection. It controls a light source module inside a snap-fit ​​housing structure to emit multi-wavelength light, allowing the light to penetrate a transfusion vessel placed inside the housing structure. The multi-wavelength light includes at least a first wavelength and a second wavelength. A photodetector module inside the snap-fit ​​housing structure acquires the light intensity transmitted through the blood via the transfusion vessel. The baseline absorbance corresponding to the first and second wavelengths is calculated, and corrected to obtain the final absorbance. The concentrations of deoxyhemoglobin and oxyhemoglobin are determined using the final absorbance and effective optical path length. The total hemoglobin concentration is obtained by adding the deoxyhemoglobin and oxyhemoglobin concentrations. The snap-fit ​​housing structure in this application fits snugly against the transparent transfusion vessel, avoiding multi-layered interference in the optical path. Dynamic monitoring of hemoglobin concentration changes is achieved based on the light intensity transmitted through the blood via the transfusion vessel, providing assistance for intraoperative transfusion assessment.

[0071] It should be understood that the sequence number of each step in the above embodiments does not imply the order of execution. The execution order of each process should be determined by its function and internal logic, and should not constitute any limitation on the implementation process of the embodiments of the present invention.

[0072] In one embodiment, a hemoglobin detection processor is provided. For example... Figure 4 As shown, the functional modules of this hemoglobin detection processor are described in detail below: Control module 41 is used to control the light source module inside the snap-fit ​​housing structure to emit multi-wavelength light, so that the multi-wavelength light penetrates the blood transfusion tube placed inside the snap-fit ​​housing structure; the multi-wavelength light includes at least a first wavelength light and a second wavelength light; The control module 41 is also used to control the photodetector module inside the snap-fit ​​housing structure to obtain the blood transmission light intensity of the multi-wavelength light to the transfusion vessel. The calculation module 42 is used to calculate the basic absorbance corresponding to the first wavelength light and the second wavelength light respectively, and to correct the basic absorbance to obtain the final absorbance. The determining module 43 is used to determine the concentration of deoxyhemoglobin and the concentration of oxyhemoglobin by the final absorbance and effective optical path length corresponding to the first wavelength light and the second wavelength light, respectively. The calculation module 42 is also used to add the deoxyhemoglobin concentration and the oxyhemoglobin concentration to obtain the total hemoglobin concentration.

[0073] In an optional embodiment, the calculation module 42 is specifically used for: The basic absorbance of the first wavelength light is calculated based on the blood transmission light intensity and the reference light intensity of physiological saline. The basic absorbance of the second wavelength light is calculated based on the blood transmission light intensity and the reference light intensity of physiological saline.

[0074] In an optional embodiment, the calculation module 42 is specifically used for: Determine whether the light absorption compensation condition is met; If the light absorption compensation condition is met, then perform light absorption compensation and proceed to the step of determining whether the turbidity compensation condition is met before continuing execution. If the light absorption compensation condition is not met, determine whether the turbidity compensation condition is met. If the turbidity compensation condition is met, then perform turbidity compensation and proceed to the step of determining whether the flow field compensation condition is met to continue execution. If the turbidity compensation condition is not met, determine whether the flow field compensation condition is met. If the flow field compensation conditions are met, flow field compensation is performed, and the process jumps to the step of determining whether the temperature compensation conditions are met to continue execution. If the flow field compensation condition is not met, determine whether the temperature compensation condition is met. If the temperature compensation conditions are met, temperature compensation is performed to obtain the final absorbance.

[0075] In an optional embodiment, the polarization compensation process is as follows: The total light intensity and linear polarization component are calculated by measuring the light intensity values ​​of polarization directions at multiple angles, and the real-time depolarization degree is calculated based on the light intensity and the linear polarization component. Calculate the ratio of the real-time depolarization degree to the clean tube wall reference value; Polarization compensation is performed by multiplying the base absorbance and the ratio.

[0076] In an optional embodiment, the turbidity compensation process is as follows: The photodetector module obtains the light intensity of the third wavelength light at the center position and the light intensity at the preset angle position in the light source module. Calculate forward scattering data based on the light intensity at the center position and the light intensity at the preset angle position; Calculate the product of the forward scattering data and the interference coefficient of turbidity at the third wavelength; Turbidity compensation is performed using the difference between the base absorbance and the product.

[0077] In an optional embodiment, the flow field compensation process is as follows: The photodetector module obtains the light intensity of the first wavelength light and the second wavelength light in the light source module at the center position and the light intensity at the preset angle position, respectively. Calculate the asymmetry of the first wavelength light based on the light intensity at the center position and the light intensity at the preset angle position; calculate the asymmetry of the second wavelength light based on the light intensity at the center position and the light intensity at the preset angle position. Flow field compensation is performed using the asymmetry corresponding to the first wavelength light and the asymmetry corresponding to the second wavelength light.

[0078] In an optional embodiment, the flow field compensation based on the asymmetry corresponding to the first wavelength light and the asymmetry corresponding to the second wavelength light includes: Calculate the absolute value of the difference between the asymmetry corresponding to the first wavelength light and the asymmetry corresponding to the second wavelength light; Flow field compensation is performed based on the absolute value of the difference and the eddy current compensation coefficient.

[0079] In an optional embodiment, the temperature compensation process is as follows: Obtain the real-time temperature and calibration temperature at the current moment; Temperature compensation is performed based on the real-time temperature and the calibrated temperature.

[0080] In an optional embodiment, the determining module 43 is specifically used for: The absorbance vector is determined based on the final absorbance corresponding to the first wavelength light and the second wavelength light, respectively. The concentrations of deoxyhemoglobin and oxyhemoglobin are determined by the absorbance vector, the absorbance coefficient matrix, and the effective optical path length.

[0081] It should be noted that the above detailed descriptions are exemplary and intended to provide further explanation of this application. Unless otherwise specified, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this application pertains.

[0082] Specific limitations regarding the hemoglobin detection processor system can be found in the limitations of the photoelectric detection method for hemoglobin detection described above, and will not be repeated here. Each module in the aforementioned device can be implemented entirely or partially through software, hardware, or a combination thereof. These modules can be embedded in hardware within or independently of the processor in the computer device, or stored in software within the computer device's memory, allowing the processor to call and execute the corresponding operations of each module.

[0083] Those skilled in the art will clearly understand that, for the sake of convenience and brevity, the above-described division of functional units and modules is used as an example. In practical applications, the above functions can be assigned to different functional units and modules as needed, that is, the internal structure of the system can be divided into different functional units or modules to complete all or part of the functions described above.

[0084] The above embodiments are only used to illustrate the technical solutions of the present invention, and are not intended to limit it. Although the present invention has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some of the technical features. Such modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of the present invention, and should all be included within the protection scope of the present invention.

Claims

1. A photoelectric detection system for hemoglobin detection, characterized in that, The photoelectric detection system includes: a photoelectric detection device and a hemoglobin detection processor connected to each other. The photoelectric detection device has a snap-fit ​​housing structure and includes: a light source module and a photodetector module. The hemoglobin detection processor is used in the following steps: The light source module inside the snap-fit ​​housing structure is controlled to emit multi-wavelength light, which penetrates the blood transfusion tube placed inside the snap-fit ​​housing structure; the multi-wavelength light includes at least a first wavelength light and a second wavelength light. The photodetector module inside the snap-fit ​​housing structure is controlled to obtain the intensity of the multi-wavelength light transmitted through the blood in the transfusion vessel. Calculate the basic absorbance corresponding to the first wavelength light and the second wavelength light respectively, and correct the basic absorbance to obtain the final absorbance; The concentrations of deoxyhemoglobin and oxyhemoglobin are determined by the final absorbance and effective optical path length corresponding to the first wavelength light and the second wavelength light, respectively. The total hemoglobin concentration is obtained by adding the concentrations of deoxyhemoglobin and oxyhemoglobin.

2. The method according to claim 1, characterized in that, The calculation of the basic absorbance corresponding to the first wavelength light and the second wavelength light respectively includes: The basic absorbance of the first wavelength light is calculated based on the blood transmission light intensity and the reference light intensity of physiological saline. The basic absorbance of the second wavelength light is calculated based on the blood transmission light intensity and the reference light intensity of physiological saline.

3. The method according to claim 1, characterized in that, The step of correcting the baseline absorbance to obtain the final absorbance includes: Determine whether the light absorption compensation condition is met; If the light absorption compensation condition is met, then perform light absorption compensation and proceed to the step of determining whether the turbidity compensation condition is met before continuing execution. If the light absorption compensation condition is not met, determine whether the turbidity compensation condition is met. If the turbidity compensation condition is met, then perform turbidity compensation and proceed to the step of determining whether the flow field compensation condition is met to continue execution. If the turbidity compensation condition is not met, determine whether the flow field compensation condition is met. If the flow field compensation conditions are met, flow field compensation is performed, and the process jumps to the step of determining whether the temperature compensation conditions are met to continue execution. If the flow field compensation condition is not met, determine whether the temperature compensation condition is met. If the temperature compensation conditions are met, temperature compensation is performed to obtain the final absorbance.

4. The method according to claim 3, characterized in that, The process of light absorption compensation is as follows: The total light intensity is calculated by measuring the light intensity values ​​from multiple angles and directions. Calculate the ratio of the real-time light intensity value to the clean pipe wall reference value; Light absorption compensation is performed by multiplying the base absorbance and the ratio.

5. The method according to claim 3, characterized in that, The turbidity compensation process is as follows: The photodetector module obtains the light intensity of the third wavelength light at the center position and the light intensity at the preset angle position in the light source module. Calculate forward scattering data based on the light intensity at the center position and the light intensity at the preset angle position; Calculate the product of the forward scattering data and the interference coefficient of turbidity at the third wavelength; Turbidity compensation is performed using the difference between the base absorbance and the product.

6. The method according to claim 3, characterized in that, The flow field compensation process is as follows: The photodetector module obtains the light intensity of the first wavelength light and the second wavelength light in the light source module at the center position and the light intensity at the preset angle position, respectively. Calculate the asymmetry of the first wavelength light based on the light intensity at the center position and the light intensity at the preset angle position; calculate the asymmetry of the second wavelength light based on the light intensity at the center position and the light intensity at the preset angle position. Flow field compensation is performed using the asymmetry corresponding to the first wavelength light and the asymmetry corresponding to the second wavelength light.

7. The method according to claim 6, characterized in that, The flow field compensation based on the asymmetry corresponding to the first wavelength light and the asymmetry corresponding to the second wavelength light includes: Calculate the absolute value of the difference between the asymmetry corresponding to the first wavelength light and the asymmetry corresponding to the second wavelength light; Flow field compensation is performed based on the absolute value of the difference and the eddy current compensation coefficient.

8. The method according to claim 3, characterized in that, The temperature compensation process is as follows: Obtain the real-time temperature and calibration temperature at the current moment; Temperature compensation is performed based on the real-time temperature and the calibrated temperature.

9. The method according to claim 3, characterized in that, The determination of deoxyhemoglobin concentration and oxyhemoglobin concentration by the final absorbance and effective optical path length corresponding to the first wavelength light and the second wavelength light, respectively, includes: The absorbance vector is determined based on the final absorbance corresponding to the first wavelength light and the second wavelength light, respectively. The concentrations of deoxyhemoglobin and oxyhemoglobin are determined by the absorbance vector, the absorbance coefficient matrix, and the effective optical path length.

10. A photoelectric detection method for hemoglobin detection, characterized in that, The method is applied to a hemoglobin detection processor in a photoelectric detection system for hemoglobin detection according to any one of claims 1-9, the method comprising: The light source module inside the snap-fit ​​housing structure is controlled to emit multi-wavelength light, which penetrates the blood transfusion tube placed inside the snap-fit ​​housing structure; the multi-wavelength light includes at least a first wavelength light and a second wavelength light. The photodetector module inside the snap-fit ​​housing structure is controlled to obtain the intensity of the multi-wavelength light transmitted through the blood in the transfusion vessel. Calculate the basic absorbance corresponding to the first wavelength light and the second wavelength light respectively, and correct the basic absorbance to obtain the final absorbance; The concentrations of deoxyhemoglobin and oxyhemoglobin are determined by the final absorbance and effective optical path length corresponding to the first wavelength light and the second wavelength light, respectively. The total hemoglobin concentration is obtained by adding the concentrations of deoxyhemoglobin and oxyhemoglobin.

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