Medical blood oxygen monitor

Abstract

The utility model discloses a medical blood oxygen monitor, which particularly relates to the field of medical instruments, and comprises a blood oxygen monitor body, a connecting line is arranged on the side wall of the blood oxygen monitor body, a connector is arranged at the other end of the connecting line, a power line is arranged at one end, far away from the connecting line, of the connector, and four groups of detection lines are arranged on one side of the power line. According to the brain blood oxygen saturation monitoring system, non-invasive detection of the brain blood oxygen saturation can be achieved, and the brain blood oxygen saturation, the tissue blood oxygen saturation and the finger pulse blood oxygen saturation can be continuously monitored; the detected cerebral blood oxygen saturation degree has blood oxygen information in a mixed blood vessel network composed of 25% of artery information and 75% of vein information, the blood oxygen information cannot be affected by pulse fluctuation information, the detection accuracy of cerebral blood oxygen is improved, in conclusion, the detection requirement of the cerebral blood oxygen saturation degree can be better met, and the detection accuracy of the cerebral blood oxygen saturation degree is improved. The non-invasive wireless accurate detection of the cerebral blood oxygen saturation is realized.

Description

Technical Field

[0001] This utility model relates to the field of medical devices, and more specifically, to a medical pulse oximeter. Background Technology

[0002] Blood oxygen saturation, the percentage of oxyhemoglobin in the total hemoglobin in human arterial blood, is an important physiological parameter reflecting the oxygen supply status of human tissues. In the early stages of blood oxygen saturation measurement, invasive methods were usually used, which involved drawing arterial blood and sending it to a blood gas analyzer for electrochemical analysis to measure the oxygen partial pressure before calculating blood oxygen saturation. However, due to the increased pain, trauma, and infection risk associated with invasive methods, they were quickly replaced by non-invasive blood oxygen saturation measurement technology. This non-invasive blood oxygen saturation measurement technology is based on the unique absorption spectra of oxygenated hemoglobin and deoxyhemoglobin in the red and infrared light regions to measure human blood oxygen saturation.

[0003] Traditionally, red and infrared light signals are converted into electrical signals and then transmitted sequentially to a filter circuit, an amplifier circuit, and an analog-to-digital converter. After filtering, amplification, and analog-to-digital conversion, the signals are transmitted to a processor. The processor receives the processed electrical signals and performs calculations to obtain blood oxygen saturation. Generally, this photoelectric detection circuit uses a dual differential amplifier circuit and dual A / D converters for processing, which results in higher processing costs.

[0004] Therefore, a medical pulse oximeter is proposed to address the above problems. Utility Model Content

[0005] In order to overcome the above-mentioned defects of the prior art, the present invention provides a medical pulse oximeter to solve the problems mentioned in the background art.

[0006] To achieve the above objectives, the present invention provides the following technical solution: a medical pulse oximeter, comprising a pulse oximeter body, characterized in that a connecting line is provided on the side wall of the pulse oximeter body, a connector is provided at the other end of the connecting line, a power cord is provided at the end of the connector away from the connecting line, and four sets of detection lines are provided on one side of the power cord, with a monitoring probe provided at the end of each set of detection lines away from the connector.

[0007] Preferably, when the near-infrared light emitted by the monitoring probe shines through the skull, the photons diffuse along multiple paths within the skull. Some of the light is absorbed by different layers of tissue: the skull, scalp, and brain, while the remaining photons are scattered in the brain tissue along the so-called "banana" model.

[0008] Preferably, the monitoring probe uses optical equipment to detect near-infrared light absorbed and scattered by brain tissue, and analysis of this emitted light spectrum reveals that the main absorption of near-infrared light in brain tissue comes from deoxygenated hemoglobin and oxygenated hemoglobin.

[0009] Preferably, the changes in hemoglobin in brain tissue monitored by the probe are explained by the Lambert-Beer Law, and the formula is as follows:

[0010]

[0011] When the near-infrared light source and monitoring probe are placed, the monitoring probe receives photons emitted after passing through the brain. Some photons are scattered and absorbed in the brain tissue. The light attenuation between the light source and the monitoring probe is described by I, where... For incident light, To monitor light, For wavelength Photon density, This is due to the attenuation of light intensity; this attenuation occurs at a wavelength of... Light absorption ( ) and scattering ( The superposition of ) leads to the conclusion that:

[0012] .

[0013] Preferably, in the detection by the monitoring probe, oxyhemoglobin (HbO2) and deoxyhemoglobin (Hb) are the main absorption channels for near-infrared light; therefore, light absorption is defined as:

[0014]

[0015] in, For hemoglobin to a specific wavelength Extinction coefficient of near-infrared light This refers to the concentration of hemoglobin. For wavelength The path length of light diffusion in tissue; this length is defined as:

[0016]

[0017] Where d is the distance between the light source and the monitoring probe. This is the path length difference coefficient, which is a correction for the length of the main photon scattering path, and is defined as follows:

[0018]

[0019] in, The absorption coefficient is... In order to be in The simplified scattering coefficient is given at wavelength. Based on the anisotropy of scattering, the simplified scattering coefficient is used to replace the scattering coefficient.

[0020] When scattering is performed, assuming a constant path length difference coefficient, the two paths can generate a difference in optical density (OD).

[0021]

[0022] This eliminates the effects of scattering.

[0023] Preferably, in the detection by the monitoring probe, each type of hemoglobin has its specific extinction coefficient and pathway length difference coefficient, and the measurements for two different wavelengths of light are as follows:

[0024]

[0025] in, , ,

[0026] and DPF are defined as and ,

[0027] Therefore, we can conclude that:

[0028]

[0029] Determine the absorption and reduction scattering coefficients and By using coefficients and formulas, the DPF value for each wavelength is obtained, and the relative changes in the concentrations of oxyhemoglobin and deoxyhemoglobin are solved. This is then used to solve a rectangular equation, and the detected near-infrared light intensity change signal is converted into changes in brain activity blood oxygen saturation, i.e., changes in hemoglobin concentration.

[0030] The technical effects and advantages of this utility model are as follows:

[0031] Compared with existing technologies, this invention enables non-invasive detection of cerebral oxygen saturation and can continuously monitor cerebral oxygen saturation, tissue oxygen saturation, and finger pulse oxygen saturation. Furthermore, the cerebral oxygen saturation detected by this invention incorporates oxygenation information from a mixed vascular network consisting of 25% arterial information and 75% venous information, and is not affected by pulse fluctuations, thus increasing the accuracy of cerebral oxygen detection. In summary, this invention better meets the needs of cerebral oxygen saturation detection, achieving non-invasive, wireless, and accurate detection, making it more suitable for clinical applications. Attached Figure Description

[0032] Figure 1 This is a schematic diagram of the overall structure of this utility model.

[0033] Figure 2 This is a schematic diagram of the structure of the near-infrared light propagation model in the brain according to this invention.

[0034] Figure 3 This is a schematic diagram of the first group of probes arranged according to this utility model.

[0035] Figure 4 This is a schematic diagram of the second group of probes arranged according to this utility model.

[0036] Figure 5 This is a schematic diagram of the third group of probes arranged according to this utility model.

[0037] The attached diagram is labeled as follows: 1. Pulse oximeter body; 2. Connecting cable; 3. Power cord; 4. Connector; 5. Detection line; 6. Monitoring probe. Detailed Implementation

[0038] The technical solutions of the present utility model will be clearly and completely described below with reference to the accompanying drawings of the embodiments. Obviously, the described embodiments are only some embodiments of the present utility model, and not all embodiments. Based on the embodiments of the present utility model, all other embodiments obtained by those of ordinary skill in the art without creative effort are within the protection scope of the present utility model.

[0039] Example 1:

[0040] As attached Figure 1 and Figure 2 The medical pulse oximeter shown includes a pulse oximeter body 1, a connecting line 2 is provided on the side wall of the pulse oximeter body 1, a connector 4 is provided at the other end of the connecting line 2, a power line 3 is provided at the end of the connector 4 away from the connecting line 2, and four sets of detection lines 5 are provided on one side of the power line 3, and a monitoring probe 6 is provided at the end of each set of detection lines 5 away from the connector 4.

[0041] Specifically, this invention achieves non-invasive detection of cerebral oxygen saturation and can continuously monitor cerebral oxygen saturation, tissue oxygen saturation, and finger pulse oxygen saturation. Furthermore, the cerebral oxygen saturation detected by this invention incorporates oxygenation information from a mixed vascular network consisting of 25% arterial information and 75% venous information, and is unaffected by pulse fluctuations, thus increasing the accuracy of cerebral oxygen detection. In summary, this invention better meets the needs for cerebral oxygen saturation detection, achieving non-invasive, wireless, and accurate detection, making it more suitable for clinical applications.

[0042] Example 2:

[0043] Based on Embodiment 1, the solution in Embodiment 1 will be further described in detail below, with reference to the specific working method described in detail:

[0044] like Figure 2 As shown, in a preferred embodiment, when the near-infrared light emitted by the monitoring probe 6 shines through the skull, the photons diffuse along multiple paths within the skull. Some of the light is absorbed by different layers of tissue: the skull, scalp, and brain, while the remaining photons are scattered in the brain tissue along the so-called "banana" model.

[0045] like Figure 2 As shown, in a preferred embodiment, the monitoring probe 6 uses optical equipment to detect near-infrared light absorbed and scattered by brain tissue. Analysis of this emitted light spectrum reveals that the main absorption of near-infrared light in brain tissue comes from deoxygenated hemoglobin and oxyhemoglobin.

[0046] like Figure 2 , Figure 3 , Figure 4 and Figure 5 As shown, in a preferred embodiment, the change in hemoglobin in brain tissue monitored by the probe 6 is explained by the Lambert-Beer Law, the formula of which is:

[0047]

[0048] When the near-infrared light source and monitoring probe 6 are placed, monitoring probe 6 receives photons emitted after passing through the brain. Some photons are scattered and absorbed in the brain tissue. The light attenuation between the light source and monitoring probe 6 is described by I, where... For incident light, To monitor light, For wavelength Photon density, This is due to the attenuation of light intensity; this attenuation occurs at a wavelength of... Light absorption ( ) and scattering ( The superposition of ) leads to the conclusion that:

[0049] .

[0050] like Figure 2 , Figure 3 , Figure 4 and Figure 5 As shown, in a preferred embodiment, during the detection by the monitoring probe 6, oxyhemoglobin (HbO2) and deoxyhemoglobin (Hb) are the main absorption channels for near-infrared light. Therefore, the absorption of light is defined as:

[0051]

[0052] in, For hemoglobin to a specific wavelength Extinction coefficient of near-infrared light This refers to the concentration of hemoglobin. For wavelength The path length of light diffusion in tissue; this length is defined as:

[0053]

[0054] Where d is the distance between the light source and the monitoring probe 6. This is the path length difference coefficient, which is a correction for the length of the main photon scattering path, and is defined as follows:

[0055]

[0056] in, The absorption coefficient is... In order to be in The simplified scattering coefficient is given at wavelength. Based on the anisotropy of scattering, the simplified scattering coefficient is used to replace the scattering coefficient.

[0057] When scattering is performed, assuming a constant path length difference coefficient, the two paths can generate a difference in optical density (OD).

[0058]

[0059] This eliminates the effects of scattering.

[0060] like Figure 2 , Figure 3 , Figure 4 and Figure 5 As shown, in a preferred embodiment, during the detection by the monitoring probe 6, each type of hemoglobin has its specific extinction coefficient and pathway length difference coefficient. The measurements for two different wavelengths of light are as follows:

[0061]

[0062] in, , ,

[0063] and DPF are defined as and ,

[0064] Therefore, we can conclude that:

[0065]

[0066] Determine the absorption and reduction scattering coefficients and By using coefficients and formulas, the DPF value for each wavelength is obtained, and the relative changes in the concentrations of oxyhemoglobin and deoxyhemoglobin are solved. This is then used to solve a rectangular equation, and the detected near-infrared light intensity change signal is converted into changes in brain activity blood oxygen saturation, i.e., changes in hemoglobin concentration.

[0067] The working process of this utility model is as follows:

[0068] This invention enables non-invasive detection of cerebral oxygen saturation and can continuously monitor cerebral oxygen saturation, tissue oxygen saturation, and finger pulse oxygen saturation. Furthermore, the cerebral oxygen saturation detected by this invention incorporates oxygenation information from a mixed vascular network consisting of 25% arterial information and 75% venous information, and is unaffected by pulse fluctuations, thus increasing the accuracy of cerebral oxygen detection. In summary, this invention better meets the needs of cerebral oxygen saturation detection, achieving non-invasive, wireless, and accurate detection, making it more suitable for clinical applications.

[0069] Finally, the following points should be noted: First, in the description of this application, it should be noted that, unless otherwise specified and limited, the terms "installation", "connection", and "linkage" should be interpreted broadly, and can be mechanical or electrical connections, or internal connections between two components, or direct connections. "Up", "down", "left", "right", etc. are only used to indicate relative positional relationships. When the absolute position of the described object changes, the relative positional relationship may change.

[0070] Secondly: The accompanying drawings of the embodiments disclosed in this utility model only involve the structures involved in the embodiments disclosed in this utility model. Other structures can refer to the general design. In the absence of conflict, the same embodiment and different embodiments of this utility model can be combined with each other.

[0071] Finally: The above description is only a preferred embodiment of the present utility model and is not intended to limit the present utility model. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of the present utility model should be included within the protection scope of the present utility model.

Claims

1. A medical oximeter comprising an oximeter body (1), characterized in that, The blood oxygen monitor body (1) side wall is provided with connecting line (2), connecting line (2) the other end is provided with connector (4), the connector (4) away from the one end of connecting line (2) is provided with power cord (3), and the power cord (3) one side is provided with four groups of detection line (5), each group of detection line (5) away from the one end of connector (4) is provided with monitoring probe (6).

2. The medical blood oxygen monitor according to claim 1, characterized in that: When the monitoring probe (6) emits near infrared waveband light irradiation through the skull, the photons diffuse along multiple paths in the skull, and a part of the light is absorbed by different layers of tissue: skull, scalp and brain, while the remaining photons are scattered in the brain tissue along the so-called "banana" model.

3. The medical blood oxygen monitor according to claim 2, characterized in that: The monitoring probe (6) detects the near infrared light absorbed and scattered by the brain tissue through optical equipment, and analyzes the outgoing light spectrum to find that the main absorption of near infrared light in the brain tissue comes from deoxyhemoglobin and oxyhemoglobin.

4. The medical blood oxygen monitor according to claim 1, characterized in that: The monitoring probe (6) detects the change of hemoglobin in the brain tissue, which is explained by Lambert-Beer law, and its formula is: ； When the near-infrared light source and the monitoring probe (6) are placed, the monitoring probe (6) receives photons emitted after passing through the brain. Some photons are scattered and absorbed in the brain tissue. The light attenuation between the light source and the monitoring probe (6) is described by I, where For incident light, To monitor light, For wavelength Photon density, This is due to the attenuation of light intensity; this attenuation occurs at a wavelength of... Light absorption ( ) and scattering ( The superposition of ) leads to the conclusion that: 。 5. The medical blood oxygen monitor according to claim 1, characterized in that: In the monitoring probe (6) detection, oxyhemoglobin and deoxyhemoglobin are the main absorption channels of near infrared light, therefore, the absorption of light is defined as: ； wherein, is the concentration of hemoglobin, is the extinction coefficient of near infrared light, is the concentration of hemoglobin, is the wavelength of light, is the diffuse path length of light of wavelength in tissue; this length is defined as: ； where d is the distance between the light source and the monitoring probe (6), is the path length difference coefficient, which is a correction for the primary scattering path length of the photons, defined as follows: ； wherein is the absorption coefficient, is the simplified scattering coefficient at the wavelength simplified scattering coefficient, the scattering coefficient is replaced by the simplified scattering coefficient according to the anisotropy of scattering; When scattering, the path length difference coefficient is assumed to be a certain value, and two paths can generate the difference of optical density OD, ； So as to eliminate the influence of scattering.

6. The medical blood oxygen monitor according to claim 1, characterized in that: In the monitoring probe (6) detection, each kind of hemoglobin has its specific extinction coefficient and path length difference coefficient, and the measurement of two different wavelength lights is as follows: ； wherein , , ; and DPF is defined as and , Therefore: ； determining absorption and scattering coefficients and By the coefficients and formula, the DPF value for each wavelength is obtained, the relative change amount of oxyhemoglobin and deoxyhemoglobin concentration is solved, which is evolved to solve the rectangular equation, and the detected near-infrared light intensity change signal is converted into the change of cerebral activity blood oxygen saturation, that is, the change of hemoglobin concentration.

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