Method for quantum magneto-optical sensing natural gradient magnetic field layering detection

Abstract

The method for quantum magneto-optical sensing natural gradient magnetic field layered detection is based on the principle that the resonance layer nuclear magnetic resonance disturbs the scattered light spectrum, thereby eliminating the influence of the skin on the content concentration of specific molecules in the detection object. By adjusting the position of the magnet, a natural gradient magnetic field is formed, under the action of the resonance layer excitation signal, nuclear magnetic resonance is generated for specific protons in the designated resonance layer of the detection object, the resonance layer nuclear magnetic resonance signal and the scattered light spectrum signal generated by the excitation light irradiation of the detection object are collected, the quantum magneto-optical sensing algorithm is used to calculate the content of specific molecules in the resonance layer of the detection object, and layered detection of the detection object is realized. The present application realizes the correlation based on quantum state between the layered nuclear magnetic resonance detection and the scattered light spectrum detection, creatively proposes the layered quantum magneto-optical sensing method, maximally simplifies the gradient magnetic field formation, reduces the cost and the volume, realizes the stripping of the influence of skin diversity, and successfully realizes the pure non-invasive IVD.

Description

Technical Field

[0001] This invention relates to the fields of the Internet and new energy, particularly to the innovative fusion of quantum mechanics, nuclear magnetic resonance spectroscopy, and scattered light spectroscopy, and specifically to the sensor subfield of medical in vitro diagnostic instruments. This invention application is one of a series of inventions previously proposed by the inventors regarding the "Quantum Magneto-optic Sensing Method," and represents a low-cost, advanced solution for further realizing this method. Specifically, it involves adjusting the position of a magnet to naturally generate a gradient magnetic field, providing a simpler and lower-cost solution compared to the traditional method of generating a gradient magnetic field using a gradient magnetic field coil. This is beneficial for realizing broad-spectrum IVD (in vitro diagnostic) products, enabling non-invasive ultra-microscopic detection of subcutaneous blood and tissue fluid in the human body, and also suitable for non-destructive detection of trace substances such as food and drugs. Background Technology

[0002] 1. Nuclear magnetic spectrum

[0003] The core of nuclear magnetic resonance (NMR) technology is a quantum phenomenon. Specifically, the magnetic moments of certain protons are magnetized in a constant longitudinal magnetic field. Because these protons have an inherent precession frequency in the magnetic field, they undergo precession resonance under the influence of a transverse excitation radio frequency magnetic field with the same precession frequency. After the excitation radio frequency magnetic field stops, the free induction decay of chemical shift occurs due to the nutation effect of protons in the chemical bonds. Based on this, the content of a specific molecule can be calculated.

[0004] Based on the resonance and relaxation processes in nuclear magnetic resonance, especially by detecting the free induction decay of chemical shifts, the characteristic magnetic spectrum of specific molecules in the analyte can be obtained. This characteristic magnetic spectrum is regarded as the "fingerprint magnetic spectrum" of a specific molecule. Through this fingerprint magnetic spectrum, the content of a specific molecule in the analyte can be further calculated.

[0005] 2. Gradient magnetic field

[0006] The gradient magnetic field is a core technology in nuclear magnetic resonance (NMR) technology, crucial for NMR detection and imaging. Currently, most gradient magnetic fields are achieved by using gradient magnetic field coils within the main magnetic field to generate a deflection magnetic field, which is then synthesized into a gradient magnetic field. This method is complex and costly; for example, existing NMR imaging systems employ this approach. A complete NMR imaging system for human detection costs around ten million yuan. Currently, no low-cost gradient magnetic field implementation solution has been found. This invention aims to provide a method that eliminates the need for deflection and gradient magnetic field coils, achieving a gradient magnetic field simply by adjusting the position of the main magnetic field magnet, thereby significantly reducing costs and equipment size.

[0007] 3. Scattered light spectrum

[0008] According to the basic principles of optics, light waves are essentially electromagnetic waves. Visible light, with frequencies between 380 and 780 nm, is an electromagnetic wave. When a beam of light (often called excitation light) strikes the surface of an object, it produces reflected, refracted, diffracted, and scattered light. Reflected, refracted, and diffracted light, in macroscopic geometric optics, represent the reactions of electromagnetic waves when they encounter another propagation medium, conforming to the laws of reflection, refraction, Fermat's law, and Malus's law. Specifically, for reflected light, the angle of reflection equals the angle of incidence, and the wavelength remains unchanged; for refracted light, the angle of refraction is a sine function of the angle of incidence and is inversely proportional to the refractive indices of the two media; for diffracted light, also known as diffraction, it refers to the physical phenomenon where light waves deviate from their original straight-line propagation when encountering an obstacle. It should be noted that reflected and refracted light are not within the scope of this invention; this invention only discusses scattered light.

[0009] Scattered light is a microscopic phenomenon that conforms to the principles of quantum mechanics. The basic principle is that charged particles, electrons, and protons within matter oscillate under the influence of incident electromagnetic waves (excitation light). The charges, accelerated by the electromagnetic waves, radiate electromagnetic waves in various directions. This process is called scattering, and the resulting electromagnetic waves are called scattered light. Scattered light can be classified into the following types.

[0010] (1) Rayleigh scattering

[0011] British physicist Rayleigh pointed out that when the diameter of a particle is much smaller than the wavelength of the excitation light, Rayleigh scattering occurs, producing scattered light with an intensity almost equal to that of the excitation light, and the scattered light has a definite scattering angle. When the particle is stationary, it produces static Rayleigh scattering with the same wavelength as the excitation light; when the particle is dynamic, it produces dynamic Rayleigh scattering, with a wavelength broadened compared to the incident light due to the Doppler shift effect; when the diameter of the particle is much larger than the wavelength of the excitation light, it also produces Mie scattering, where the intensity of the scattered light is independent of the excitation light wavelength. Rayleigh scattering is an elastic form of scattered light.

[0012] (2) Brillouin scattering

[0013] French-American scientist Brillouin's research on inelastic scattered light involving acoustic phonons and magnons indicates that the elementary excitations generated and annihilated during the interaction of light quanta with the matter emitting the scattered light are only low-energy acoustic phonons or magnons, with energies ≤0.124 meV, and interacting with photons on the order of 10-1. -18 ~10 -17 And it is coherent.

[0014] (3) Raman scattering light

[0015] Indian physicist Raman discovered this phenomenon in his research on scattered light and was awarded the 1930 Nobel Prize in Physics. This phenomenon is the process by which light quanta interact with the matter emitting the scattered light, creating and annihilating elementary excitations. These excitations include all types of elementary excitations and the rotational and vibrational states of atoms and molecules. Two photons transition between three energy levels (ground, virtual, and final states), creating and annihilating an elementary excitation (one from phonons, magnons, electrons, or plasmons). Its energy ranges from a few to several hundred, and its interaction with photons is on the order of 10^6. -14 Furthermore, it exhibits incoherence. This includes Stokes scattered light with a wavelength longer than the excitation wavelength and anti-Stokes scattered light with a wavelength shorter than the excitation wavelength.

[0016] (4) Thomson scattering light

[0017] British physicist J.J. Thomson discovered that the electric field of an incident electromagnetic wave causes elastic scattering of free charged particles within it, characterized by the scattered wave having the same wavelength as the excitation light. Furthermore, the primary cause of particle acceleration comes from the electric field component of the incident wave, while the effect of the magnetic field is negligible. The particles then begin to move in the direction of the electric field oscillation, thus producing electromagnetic dipole radiation. Thomson's achievement earned him the 1906 Nobel Prize in Physics.

[0018] (5) Compton scattering

[0019] American physicist John Compton discovered the process by which incident excitation photons collide inelastically with electrons in atoms and are scattered. During the collision, the incident photon transfers some energy to the electron, causing it to detach from the atom and become a recoil electron, while the energy and direction of the scattered photon change. The phenomenon where the wavelength of the scattered light increases due to energy loss is called the Compton phenomenon; the phenomenon where the wavelength of the scattered light decreases due to the photon gaining energy is called the inverse Compton phenomenon. Compton's achievements earned him the 1927 Nobel Prize in Physics.

[0020] (6) Fluorescence

[0021] When excitation light shines on certain atoms, the energy of the light causes some electrons around the atomic nucleus to jump from their original orbits to higher-energy orbits, that is, from the ground state to a higher-level excited singlet state. These higher-level singlet states are unstable and will revert to the ground state. At this time, the energy is released in the form of photons, thus producing fluorescence. In most cases, the wavelength of fluorescence is longer and the energy is lower than that of the excitation light. However, when the absorption intensity is high, two-photon absorption may occur, resulting in a situation where the radiation wavelength is shorter than the absorption wavelength. When the radiation wavelength is equal to the absorption wavelength, it is called resonant fluorescence. A common example is that a substance absorbs ultraviolet light and emits visible fluorescence. The fluorescent lamps in our daily lives work on this principle. The phosphor coated on the lamp tube absorbs the ultraviolet light emitted by the mercury vapor in the tube, and then the phosphor emits visible light, making it a visible light source that can be used for illumination.

[0022] It should be noted that, in this invention application, considering that both fluorescence and scattered light share a common foundation in quantum mechanics, for ease of explanation, we include fluorescence in the category of scattered light, treating them as the same category.

[0023] 4. Current Research Accumulation of Quantum Magneto-Optical Sensing Methods

[0024] Since 2022, the inventors' team has applied for and been granted three Chinese invention patents by the China National Intellectual Property Administration: "Quantum Magneto-optic Sensing Method (Chinese Patent No. CN114441507B)," "Quantum Magneto-optic Sensor (Chinese Patent No. CN114441506B)," and "Quantum Magneto-optic Multidimensional Sensing Method (Chinese Patent No. CN115452803B)." These patents represent similar innovations previously applied for by the inventors' team. Their main innovations are: 1. Simultaneously performing nuclear magnetic resonance (NMR) magnetic spectrum detection and surface-scattered light spectral detection on a detector containing specific protons. 2. Establishing a quantum mechanical equation relating the magnetic spectrum and the spectral spectrum, and solving for the content of specific protons and molecules in the detector. 3. Proposing a thorny sphere distribution model for quantum scattered light and establishing a mathematical model for the statistical distribution of microscopic atoms and macroscopic detectors.

[0025] The aforementioned achievements are the first to propose and successfully solve the theoretical, computational, implementation, and structural design problems related to the correlation between nuclear magnetic resonance magnetic spectroscopy and scattered light spectroscopy. This invention is a further development and continuation of these studies, aiming to further propose a method for layered detection of natural gradient magnetic fields in 0-3 dimension using quantum magneto-optical sensing on the analyte. This will enable more precise positioning and measurement, and better application in products such as non-invasive detection. For example, a major problem encountered in non-invasive in vitro detection of the human body (such as IVD products) is interference from the skin. Specifically, when detecting trace substances in subcutaneous tissue, tissue fluid, and blood vessels in vitro, neither magnetic spectrum nor spectral spectrum can counteract the diverse interference from the skin. However, multi-dimensional positioning measurement can perfectly solve this problem.

[0026] 5. Brief description of existing scattered light detectors

[0027] In vitro diagnostic products

[0028] In vitro diagnostic (IVD) products, which perform medical tests outside the human body, differ from surgery and blood tests. Non-invasive IVD, in particular, can complete the test without breaking the skin, making it increasingly popular with medical institutions and those being tested. However, because non-invasive IVD involves examining the internal organs (such as blood, tissue fluid, and subcutaneous tissue) through the skin, the innovation of its theoretical models and the technical implementation are extremely difficult. For example, a single MRI system has been the subject of 17 Nobel Prizes (12 in total), and Raman spectroscopy is also a Nobel Prize-winning achievement in physics.

[0029] Trace substance detection products

[0030] For some trace substances containing specific protons that can form nuclear magnetic resonance, whether in a solution of pure atomic structure or a mixture of molecular structure, detection is quite difficult when their content is very small. For example, the detection of trace substances in food, trace substances in medicine, and highly toxic substances, etc., and the need for such detection exists.

[0031] Spectroscopic detection products

[0032] Compared to other detectors in the field of measurement, scattered light detectors are still in the early stages of development. Although in recent years, research reports on some specialized self-developed equipment have occasionally been published in scientific journals to meet the needs of scientific research, such as experimental equipment for femtosecond laser detection, high-precision Raman spectroscopy acquisition equipment, and array laser imaging equipment, the inventors have identified the following types of commercialized equipment, which are described below.

[0033] (1) Coaxial Scattering Light Detector Complete Unit

[0034] Coaxiality refers to the fact that the emission of excitation light and the reception of scattered light share the same optical axis at the detection point. This is the conventional method for current scattered light detection. For example, the vast majority of existing Raman detectors, fluorescence detectors, and even active spectrometers almost invariably employ a coaxial structure.

[0035] (2) Coaxial spectral probe

[0036] In order to reduce costs and emphasize versatility, some manufacturers have even designed the excitation light emission and the scattered light reception into a product called a spectral probe, whose structural principle is still the coaxial structure of excitation light and receiving light.

[0037] (3) In vitro diagnostic products

[0038] Typical in vitro diagnostic products based on coaxial structures include IVD (In Vitro Diagnostic Products). Because they utilize external methods for medical detection, unlike surgery and blood tests, especially non-invasive IVD which can complete the test without breaking the skin, they are increasingly welcomed and valued by medical institutions and those being tested. However, since non-invasive IVD probes the internal organs (such as blood, tissue fluid, and subcutaneous tissue) through the skin, the innovation of its theoretical model and the difficulty of its technical implementation are extremely challenging. For example, a single MRI system has been the subject of 17 Nobel Prizes (12 in total), and Raman spectroscopy is also a Nobel Prize-winning achievement in physics.

[0039] (4) Trace substance detection products

[0040] Trace substance detection products based on coaxial structure: For example, for some ultra-trace substances containing specific protons that can form nuclear magnetic resonance, whether in a pure atomic solution or a molecular mixture, it is difficult to detect them when their content is very small. For example, trace substances in food, trace substances in medicine, and highly toxic substances also have this need.

[0041] (5) Raman spectroscopy

[0042] Raman spectroscopy based on coaxial structures: The core theory of Raman spectroscopy is the Raman effect (Raman scattering, Chandrasekhara Venkata Raman, 1888-1970, Indian physicist). The Raman effect was discovered in 1928 and awarded the Nobel Prize in Physics in 1930. The core principle of the Raman effect is also a quantum phenomenon. When photons of excitation light of a specific wavelength collide with electrons outside the nucleus of an atom, the electrons absorb the energy of the photons, producing scattered photons according to the principle of energy conservation. The vast majority of these collisions occur elastically, and the wavelength of the ejected photons is the same as the excitation light wavelength; this is called Rayleigh scattering. A small portion of these collisions occur inelastically. In these cases, due to the energy level transitions of the electrons, some energy is absorbed or released, so the wavelength of the scattered light is not equal to the excitation light wavelength; this is called Raman scattering. Raman scattering is further divided into three categories based on wavelength: Brillouin scattering, where the wavelength of the scattered light is relatively close to that of the excitation light (1–10 / cm⁻¹); Stokes scattering, where the wavelength of the scattered light is significantly larger than that of the excitation light (>10 / cm⁻¹); and anti-Stokes scattering, where the wavelength of the scattered light is significantly smaller than that of the excitation light. The spectrum composed of Brillouin scattering, Stokes scattering, and anti-Stokes scattering is called Raman spectroscopy.

[0043] Based on the molecular bonds and atomic structure of a specific molecule, a fixed Raman spectrum can be generated, which is also known as the "fingerprint spectrum" of the specific molecule. Through this fingerprint spectrum, the content of the specific molecule in the detector can be further calculated.

[0044] 6. Shortcomings of existing technology

[0045] From the perspective of quantum magneto-optical sensing technology (Chinese patents CN114441507B for "Quantum Magneto-optical Sensing Method", CN114441506B for "Quantum Magneto-optical Sensor", 202211270064.4 for "Quantum Scattered Light Distribution Detector Based on Multi-axis and Multi-mode", and CN115452803B for "Quantum Magneto-optical Multi-dimensional Sensing Method"), existing technologies do not employ a low-cost gradient magnetic field, and therefore fail to achieve low-cost, layered detection of the analyte. This not only fails to solve the problems of low cost and small size of gradient magnetic fields, thus hindering the reduction of overall equipment cost and size, but also prevents the ability to detect subcutaneous substances through the surface of the analyte in a small volume. For example, in the detection of glucose in human tissue fluid, due to the diversity of skin, accurate detection of subcutaneous tissue cannot be achieved without eliminating skin interference.

[0046] Therefore, using gradient magnetic fields is important and necessary for achieving layered detection of analytes.

[0047] 7. Purpose, Intent, and Contribution of the Invention

[0048] Based on the analysis of the shortcomings of the aforementioned background technology and existing technology, the inventors have innovated this invention patent application—"Method for Detecting Layered Natural Gradient Magnetic Fields in Quantum Magneto-Optical Sensing." The main objectives of this invention include:

[0049] (1) By adjusting the position of the magnet to naturally generate a gradient magnetic field, low-cost layered detection of the analyte can be achieved.

[0050] (2) Design a quantum magneto-optical sensing algorithm to realize the specific molecular content detection calculation for the layering of the analyte.

[0051] The main intentions and contributions of this invention include:

[0052] (1) Structural contribution: By using low-cost magnetic fields, including permanent magnets, and by adjusting the position of the magnets to generate a gradient magnetic field, the cost and volume are reduced to the greatest extent.

[0053] (2) Theoretical contribution: A metrological magneto-optical sensing algorithm was designed to accurately detect and calculate the specific molecular content of the stratified analyte.

[0054] (3) Intent of the invention: To provide a method for detecting the natural gradient magnetic field layer by quantum magneto-optical sensing with low cost and small volume. Summary of the Invention

[0055] 1. Core Idea of ​​the Invention

[0056] Gradient magnetic field and K-space

[0057] In nuclear magnetic resonance theory, the gradient magnetic field is a magnetic field superimposed on the main magnetic field. Since the nuclear magnetic resonance frequency of a specific proton of the sample at a certain point in the magnetic field is linearly proportional to the magnitude of the synthesized magnetic field at that point, by changing the magnitude of the synthesized magnetic field at each detection point in a detection area, it is possible to scan the nuclear magnetic resonance points. Through scanning, the entire space of the entire detection area can be traversed.

[0058] Formula 1.1 explains the principle of NMR frequency calculation, Formula 1.2 defines the NMR frequency at point x in the gradient magnetic field, and Formula 1.3 represents the gradient magnetic field tensor and the partial differential equations in K-space. Those skilled in the field should understand the basic principles of NMR.

[0059] ω0=γB0 1.1

[0060] ω x =γ(B0+xG x )=ω0+Δω x 1.2

[0061]

[0062] Where ω0 is the nuclear magnetic resonance frequency in the static magnetic field, γ is the gyromagnetic ratio of a specific proton, and B0 is the magnitude of the static main magnetic field. x G is the nuclear magnetic resonance frequency at point x in the gradient magnetic field, where x is the position in the gradient magnetic field. x Let Δω be the field gradient. x is the offset of the nuclear magnetic resonance. T is the tensor of the gradient magnetic field.

[0063] In the structure of nuclear magnetic resonance (NMR) equipment, the gradient magnetic field is generated by a specially designed gradient magnetic field coil. This design involves energizing the gradient magnetic field coil to generate excitation, which is superimposed on the main magnetic field, causing a superimposed variation in the magnitude of the main magnetic field along a certain axial direction, as shown in Equation 1.3, thus generating the gradient magnetic field. This approach is structurally complex, bulky, and requires significant electrical energy, resulting in high costs.

[0064] Natural gradient magnetic field formation and location function

[0065] According to magnetic field theory, assuming the magnetic field strength of a magnet is B, the magnetic field strength at a distance R from the magnet will exhibit a position function relationship according to Formula 1.4. For a pair of magnets with uniform magnetic fields, assuming the magnetic poles are planar, if the N-pole and S-pole are parallel, the magnetic field strength at the midpoint of the poles is equal on a reference intermediate plane parallel to the poles. If the N-pole and S-pole form a non-zero angle, i.e., they are not parallel, then according to Formula 1.4, the magnetic field strength will gradually change on the symmetrical reference intermediate plane, i.e., a gradient magnetic field will appear. Through careful arrangement, a linear gradient magnetic field will appear within a certain range of the reference intermediate plane.

[0066] B∝R -2 1.4

[0067] It should be noted that position function formula 1.4 is a conceptual formula. In specific designs, further refinement is needed based on the shape of the magnet, the position of the magnet arrangement, and the selection of the reference intermediate plane to provide a detailed position function. Furthermore, the reference intermediate plane can also be normalized to a central axis, such as the X-axis in steps 2.3 and 2.4 of the invention below.

[0068] Theoretical basis of quantum scattering light

[0069] Based on the principle of light scattering, at the microscopic level, the generation of all scattered light conforms to the principles of quantum mechanics. It is produced by the interaction of excited photons with the outer electrons of matter atoms, conforming to the energy wave function law of quantum mechanics. Using the detection point irradiated by the excited light as the center of a sphere and the incident light as the reference, a spherical polar coordinate system is established. The scattered light, according to the law of the energy wave function, will exhibit a probability distribution and an angular distribution on this sphere. By detecting this probability and angular distribution, high-probability regions can be found, thus identifying the so-called "highlights," and further, the probability distribution map of the scattered light can be determined.

[0070] Quantum nuclear magnetic energy wave function

[0071] The formulas for calculating the energy wave function include, but are not limited to:

[0072] Formula 1.5 is the Laplace operator in Cartesian three-dimensional coordinates; Formula 1.6 is the formula for calculating the reduced Planck constant; Formula 1.7 is the Schrödinger equation in Cartesian three-dimensional coordinates; Formula 1.8 is the Laplace operator in spherical polar coordinates; Formula 1.9 is the Laplace equation in spherical polar coordinates; Formula 1.10 is the Hamiltonian operator; Formula 1.11 is the Schrödinger equation in spherical polar coordinates; Formula 1.12 is the formula for calculating the wave function of a particle; Formula 1.13 is the formula for calculating the probability density of a particle; Formula 1.14 is the overall probability function for n quantum numbers; and Formula 1.15 is the formula for calculating the optimal probability interval.

[0073]

[0074]

[0075] |Ψ(x,t)| 2 =|c1| 2 |ψ1(x)| 2 +|c2| 2 |ψ2(x)| 2 +2|c1c2||ψ1(x)ψ2(x)|cos(ωt+δ)1.13

[0076]

[0077] Where ψ2(x) is the wave function of the particle, |Ψ(x,t)| 2 Here, c1 and c2 are complex constants, t is any time, ω is the oscillation frequency, θ is the azimuth angle, φ is the elevation angle, r is the radius, δ is the Dirac impact function, n is the quantum number, and |ψ| is the probability density of the particle. n (x)| 2 Q is the probability density of the nth particle. n Q is the overall probability function for n particles. ns It is the optimal probability interval, where s is between Q and Q. n A threshold within a range of sizes.

[0078] Preferably, the quantum state and magneto-optical angle in nuclear magnetic resonance are determined by the step of an electron being excited by excitation light, transitioning from a low energy level to a high energy level, and then falling back from the high energy level to the original low energy level, thereby releasing photons, and using the probability distribution of these released photons as the probability distribution of the Raman spectral signal.

[0079] Preferably, the step involves calculating the probability distribution of the Raman spectral signal based on the quantum states of all specific protons in the detector and the magneto-optical angle in nuclear magnetic resonance.

[0080] Preferably, the step involves determining the position with the highest probability in the probability distribution of the Raman spectral signal, using this position as the receiving position for the Raman scattered light, receiving the Raman scattered light, and obtaining the optimal nuclear magnetic resonance spectrum.

[0081] Preferably, the quantum state includes the spin of the atomic nucleus, the spin of a specific proton, electronic energy levels, electron cloud probability, and electronic energy level transitions.

[0082] In practical design, the formulas in this invention are just one way of expressing the concepts. Different academic schools of thought may use different ways of writing formulas, all of which are included in this invention. Intermediate-level designers in the industry should be able to design by referring to publicly available and commonly used materials.

[0083] Correlation between nuclear magnetic resonance spectrum and scattered light spectrum

[0084] The nuclear magnetic resonance spectrum includes at least the following: main magnetic field strength, excitation radio frequency, gradient magnetic field strength, nuclear magnetic resonance frequency, coordinates of nuclear magnetic resonance points, relaxation signal (free induction decay FID), longitudinal relaxation time T1, transverse relaxation time T2, and detection time.

[0085] The scattered light spectrum includes at least frequency shift, intensity, and detection time.

[0086] Scattered light attenuation

[0087] Due to differences in the properties of the analyte, when the excitation light illuminates the detection point of the analyte, it penetrates to a certain depth along the optical axis of the excitation light in a gradient-attenuated manner, depending on the wavelength of the excitation light and the properties of the analyte. In other words, the energy of the photons gradually decreases to zero as the depth of penetration increases. This depth is considered the maximum detection depth. The scattered light emitted to the detection point decreases as the energy of the excitation light photons decreases. When using an infrared laser with a wavelength of 785nm as the excitation light, it can penetrate approximately 2mm to 3mm into human skin. At this depth, the excitation light will gradually attenuate with changes in depth. The generated scattered light also gradually weakens with increasing depth. In this patent application, we can refer to a linear attenuation method to correct the scattered light intensity of the detection layer.

[0088] The maximum number of detection layers is calculated based on the depth to which the excitation light can penetrate the target (e.g., skin). For example, for a 785nm laser, the maximum depth in the skin of a human fingertip is approximately 3.0mm, while the depth in the epidermis and dermis is approximately 1.2mm. For glucose (molecular formula C6H4H4N2), the maximum depth is much greater. 12 O6) or sodium chloride (molecular formula NaCl) or progesterone (molecular formula C 21 H 30O2 detection needs to be performed in the subcutaneous tissue below the dermis. Therefore, it's necessary to calculate the NMR and scattered light spectra of the detection layer from 1.2mm to 2.5mm. Specifically, during NMR, layered calculations are performed in a gradient magnetic field. For example, if the volumetric size is 1.40mm, the first volumetric layer is 1.4mm thick, which is the area between the epidermis and dermis. We don't need to detect glucose levels in this layer. The second volumetric layer is between 1.4mm and 2.8mm, which is the location where we need to detect glucose. The excitation magnetic field frequency for this layer is calculated, and based on this frequency, the 1.4mm to 2.8mm tissue under the finger's skin enters a hydrogen NMR state. The scattered light spectrum obtained under this NMR state is then subtracted from the attenuation of the first layer (1.4mm) to obtain the scattered light spectrum signal of this detection layer. Based on this, and by comparing with a database, the detection content of the specific molecule—glucose—is calculated.

[0089] Differences between nuclear magnetic resonance spectra and scattered light spectra of different molecular structures

[0090] For different molecular structures containing specific protons, the resulting nuclear magnetic resonance (NMR) and scattered light spectra will differ due to variations in covalent bonds and the concentration of the specific molecule in the analyte. When it is necessary to detect the concentration of a specific molecule, professionals need to establish and solve equations based on these differences to determine the concentration of that specific molecule. Alternatively, they can rely on the analyte (glucose C6H)... 12 O6 or sodium chloride (NaCl) or progesterone C 21 H 30 The comparison database established by measuring O2 is used to search and determine the results.

[0091] Off-axis tunable mode of scattered light spectrum

[0092] Based on the shortcomings of existing technologies, a new scattered light detector is designed to change the existing coaxial mode of excitation light and collected scattered light to an off-axis mode, and the off-axis angle is adjustable. By adjusting the off-axis angle, the position of the strongest scattered light can be found.

[0093] 2. Implementation steps of the present invention

[0094] The purpose, intent, and contribution of this invention are achieved through the following technical solution and working steps.

[0095] 2.1 Basic Structure

[0096] This invention, as a method for detecting the layered magnetic field of a natural gradient in quantum magneto-optical sensing, includes the following steps:

[0097] M1000 Steps: Set the magnet position to create a natural gradient magnetic field, and obtain the position function between the position and the magnetic field strength in the natural gradient magnetic field.

[0098] This includes, but is not limited to, placing a specific proton that can undergo nuclear magnetic resonance in a natural gradient magnetic field, dividing the detector into one or more resonance layers along the direction perpendicular to the natural gradient magnetic field from the outside to the inside, using the resonance layer excitation signal to excite the specific protons in the corresponding resonance layer of the detector to generate nuclear magnetic resonance, and collecting the nuclear magnetic induction signal of the resonance layer through an induction coil.

[0099] M3000 steps: The detector is irradiated from the outside with excitation light, the scattered light signal is collected, and the characteristic peak signal of the molecular bond of a specific proton in a specific molecule, including but not limited to, is decomposed in the scattered light signal.

[0100] M4000 step: A quantum magneto-optical sensing algorithm, which uses the resonant layer nuclear magnetic induction signal and the characteristic peak signal as independent variables, is used to calculate the content of specific molecules in the detected substance.

[0101] 2.2 Quantum Magneto-optic Sensing Algorithm

[0102] Based on the aforementioned basic solution, the present invention specifically includes, but is not limited to, one or more combinations of the following:

[0103] Quantum magneto-optical sensing algorithms include, but are not limited to, empirical difference algorithms, correlation difference algorithms, or joint verification algorithms, specifically including:

[0104] M4100 steps: Empirical Differential Algorithm, specifically including but not limited to:

[0105] Based on the characteristic peak signal and the nuclear magnetic resonance induction signal of one or more resonance layers, the maximum depth that can be reached when the excitation light irradiates the analyte is used to divide one or more irradiation layers from the outside to the inside along the direction perpendicular to the natural gradient magnetic field. The irradiation layers include, but are not limited to, one or more resonance layers. Based on the empirical data of the analyte, the characteristic peak signal of the irradiation layer is decomposed and calculated, and the content of specific molecules in the analyte is calculated based on the nuclear magnetic resonance induction signal of the resonance layer and the characteristic peak signal of the irradiation layer.

[0106] Empirical data includes, but is not limited to, historical data obtained through testing, corresponding to the relationship between the NMR signal data of the irradiated layer and the resonance layer, the characteristic peak signal data of the irradiated layer, and the content data of specific molecules in the analyte.

[0107] M4200 steps: Correlation difference algorithm, including but not limited to:

[0108] Based on the characteristic peak signal and the nuclear magnetic resonance induction signal of one or more resonance layers, using the maximum depth that can be reached when the excitation light irradiates the detector, one or more irradiation layers are divided from the outside to the inside along the direction perpendicular to the natural gradient magnetic field. The irradiation layer includes one or more resonance layers. Based on the correlation function of the change of characteristic peak signal of specific protons included in specific molecules in the detector due to magnetization and nuclear magnetic resonance, the characteristic peak signal of the irradiation layer is decomposed and calculated. The content of specific molecules in the detector is calculated based on the nuclear magnetic resonance induction signal of the resonance layer and the characteristic peak signal of the irradiation layer.

[0109] The calculation of the correlation function includes, but is not limited to, one or a combination of the following methods:

[0110] Based on methods including but not limited to Rayleigh equations and probability calculations, the characteristic peak signals of the irradiated layer are decomposed and calculated.

[0111] Based on cloud-based statistical methods using artificial intelligence and big data, the characteristic peak signals of the irradiation layer are decomposed and calculated.

[0112] Based on methods including but not limited to the integration of artificial intelligence system plug-ins, the characteristic peak signals of the irradiation layer are decomposed and calculated.

[0113] Based on training with a multimodal large language model using artificial intelligence, the characteristic peak signal of the illumination layer is decomposed and calculated.

[0114] Based on, but not limited to, the physical state of the detected substance, such as solid, liquid, gas, and crystalline states, the characteristic peak signal of the irradiated layer is decomposed and calculated.

[0115] Based on factors including but not limited to the temperature, concentration, molecular structure, and types of mixed substances of the analyte, the characteristic peak signals of the irradiated layer are decomposed and calculated.

[0116] M4300 steps: Joint verification algorithm, including but not limited to:

[0117] Simultaneously, empirical difference algorithm and correlation difference algorithm are used to calculate the characteristic peak signal of the irradiated layer and the content of specific molecules in the detector, respectively.

[0118] Based on the joint verification function, the content of characteristic molecules in the analyte is calculated.

[0119] The calculation of the joint check function also includes, but is not limited to, one or a combination of the following methods:

[0120] Based on the weight parameters of the set empirical difference algorithm and correlation difference algorithm, the content of specific molecules in the detected substance is calculated by jointly verifying each characteristic peak.

[0121] Based on the theoretical parameters of the empirical difference algorithm and the correlation difference algorithm, the content of specific molecules in the analyte is calculated by jointly verifying each characteristic peak.

[0122] Based on the temperature of the analyte, the various characteristic peaks are jointly verified, and the content of specific molecules in the analyte is calculated.

[0123] Based on the concentration of the analyte, the various characteristic peaks are jointly verified, and the content of specific molecules in the analyte is calculated.

[0124] Based on the concentration and speciation of the analyte, the content of specific molecules in the analyte is calculated by jointly verifying each characteristic peak.

[0125] 2.3 Bar magnet, position and coordinate system

[0126] Based on the aforementioned basic solution, the present invention specifically includes, but is not limited to, one or more combinations of the following:

[0127] The M1000 process specifically includes:

[0128] M1110 Procedure: The magnets are composed of pairs of bar-shaped rectangular hexagonal permanent magnets, electromagnets, or superconducting magnets. Each pair of magnets consists of two magnets with a uniform magnetic field. The N pole of one magnet and the S pole of the other magnet are arranged face to face. The edges of the N pole magnet and the S pole magnet form a plane with the X-axis. The two edges are symmetrically distributed on both sides of the X-axis and intersect the X-axis at the origin. The angles between the two edges and the X-axis are both greater than 0 degrees and are equal. The position of the object to be detected on the X-axis is the location point. Excitation coils and induction coils are arranged according to the requirements of nuclear magnetic resonance.

[0129] M1120 Step: Establish a one-dimensional coordinate system along the X-axis using a pair or more magnets. By adjusting the position of the magnets, the magnitude of the magnetic field generated between the magnets moves along the X-axis, presenting a gradually increasing or decreasing one-dimensional gradient magnetic field.

[0130] M1130 Step: Using the direction of the magnetic field naturally generated between a pair or more magnets as the Z-axis direction, arrange the Z-axis perpendicular to the X-axis to establish a two-dimensional coordinate system of X-axis and Z-axis. By adjusting the position of the magnets, the magnitude of the magnetic field generated between the magnets is made to move along the X-axis and along the Z-axis, presenting a two-dimensional gradient magnetic field that gradually increases or decreases.

[0131] M1140 Step: Establish a three-dimensional coordinate system of X, Y, and Z, with the direction of the magnetic field naturally generated between a pair of magnets as the Z-axis and the direction perpendicular to both the X and Z axes as the Y-axis. By adjusting the position of the magnets, the magnitude of the magnetic field generated between the magnets is made to gradually increase or decrease along the X-axis, Z-axis, and Y-axis directions, presenting a three-dimensional gradient magnetic field.

[0132] In fact, based on the latest inventions in permanent magnets in the industry, a high-strength neodymium iron boron permanent magnet is more suitable for the application of this invention. Furthermore, with the advancement of high-temperature superconductors, magnets constructed using inexpensive high-temperature superconductors will also be incorporated into the application of this invention.

[0133] 2.4 Cylindrical magnet, position and coordinate system

[0134] Based on the aforementioned basic solution, the present invention specifically includes, but is not limited to, one or more combinations of the following:

[0135] The M1000 process also includes, but is not limited to:

[0136] M1210 Steps: The magnet is composed of a cylindrical permanent magnet, electromagnet, or superconducting magnet. The N and S poles of the magnet are arranged at both ends of the cylindrical body, and the diameters at both ends are different, forming a trapezoidal shape. The central axis of the cylindrical body is taken as the X-axis, and the position of the object to be detected on the X-axis is taken as the location point.

[0137] M1220 steps: Establish a one-dimensional coordinate system along the X-axis. By adjusting the position of the object being detected, the magnitude of the magnetic field is obtained by moving along the X-axis to present a gradually increasing or decreasing one-dimensional gradient magnetic field. The excitation coil and induction coil are arranged along the vertical direction of the X-axis.

[0138] M1230 steps: Establish a two-dimensional coordinate system with X and Z axes, arrange a Z gradient coil perpendicular to the X axis, generate a Z gradient magnetic field that gradually increases or decreases as it moves along the Z axis, and form a two-dimensional gradient magnetic field together with the X gradient magnetic field, and arrange excitation coil and induction coil.

[0139] M1240 steps: Establish a three-dimensional coordinate system of X, Y, and Z, arrange a Z gradient coil perpendicular to the X-axis and a Y gradient coil perpendicular to both the X and Z axes. The Z gradient coil generates a gradually increasing or decreasing Z gradient magnetic field that moves along the Z-axis. The Y gradient coil generates a gradually increasing or decreasing Y gradient magnetic field that moves along the Y-axis. Together with the X and Z gradient magnetic fields, they form a three-dimensional gradient magnetic field. Excitation coils and induction coils are also arranged.

[0140] M1150 Steps: Adjust the position of the magnets, specifically including:

[0141] M1151 Step: A pair of magnets are placed symmetrically about the X-axis, creating a natural gradient magnetic field between the angles formed by the two magnets.

[0142] M1152 Steps: Multiple pairs of magnets are placed symmetrically about the X-axis, creating a natural gradient magnetic field between the angles formed by the multiple pairs of magnets.

[0143] M1153 Steps: A pair of magnets are placed symmetrically parallel to the X-axis to form a natural gradient magnetic field at the entrance of the strip formed by the pair of magnets.

[0144] M1154 Steps: Multiple pairs of magnets are placed symmetrically parallel to the X-axis to form a natural gradient magnetic field at the entrance of the long strip formed by the multiple pairs of magnets.

[0145] In fact, based on the latest inventions in permanent magnets in the industry, a high-strength neodymium iron boron permanent magnet is more suitable for the application of this invention. Furthermore, with the advancement of high-temperature superconductors, magnets constructed using inexpensive high-temperature superconductors will also be incorporated into the application of this invention.

[0146] 2.5 Position Functions

[0147] Based on the aforementioned basic solution, the present invention specifically includes, but is not limited to, one or more combinations of the following:

[0148] The M1000 process also includes:

[0149] M1300 steps: Position functions include, but are not limited to:

[0150] M1310 steps: The position function includes, but is not limited to, the magnetic field strength at the X-axis position in a one-dimensional coordinate system of the natural gradient magnetic field, or the X-axis / Z-axis position in a two-dimensional coordinate system, or the X-axis / Z-axis / Y-axis position in a three-dimensional coordinate system.

[0151] M1320 Steps: The actual measurement method uses a magnetic field strength sensor to measure the position function at each location point in a natural gradient magnetic field of a specified environment.

[0152] M1330 Steps: The calculation method is based on the geometric relationship between the position of the magnet and the magnetic field strength. For each position point, the position function is calculated to obtain the position function.

[0153] 2.6 Temperature compensation and magnetic field compensation

[0154] Based on the aforementioned basic solution, the present invention specifically includes, but is not limited to, one or more combinations of the following:

[0155] The M1000 process also includes:

[0156] M1410 Step: Use a temperature sensor to monitor the magnetic field temperature by means of cooling, heating or natural ambient temperature.

[0157] M1420 Step: Based on the magnetic field temperature, perform positive linear, negative linear, or nonlinear temperature compensation for the natural gradient magnetic field itself, according to the magnitude of the natural gradient magnetic field.

[0158] M1430 Steps: Use constant temperature control for the magnetic field temperature, and perform positive linear, negative linear, or nonlinear temperature compensation for the natural gradient magnetic field itself.

[0159] M1510 Step: Use a magnetic field sensor to obtain the measured magnetic field strength at the location point, and calculate the magnetic field deviation compensation for the natural gradient magnetic field based on the difference between the measured magnetic field strength and the set magnetic field strength at the location point.

[0160] 2.7 Resonance Layer

[0161] Based on the aforementioned basic solution, the present invention specifically includes, but is not limited to, one or more combinations of the following:

[0162] The M2000 process also includes:

[0163] M2100 step: According to the position function, in the natural gradient magnetic field, connect one or more adjacent position points whose absolute difference in magnetic field strength is less than the layer error to form a resonant layer, and so on, in the natural gradient magnetic field, divide all position points into several resonant layers, wherein the difference in layer error on the X-axis is the thickness of the resonant layer.

[0164] M2200 steps: Based on the magnetic field strength of a resonance layer and the gyromagnetic ratio of a specific proton, calculate the frequency of the resonance layer excitation signal of that resonance layer, and calculate the frequency of the resonance layer excitation signal of all resonance layers.

[0165] M2300 steps: Starting from the origin, number all resonant layers and their corresponding excitation signals from 1, denote the largest resonant layer number as n, and calculate R1 to R2 for all resonant layers. n The frequencies of the excitation signals of the corresponding resonant layers are used to obtain F1 to F. n .

[0166] M2400 Steps: From the first resonant layer to the last resonant layer, sequentially use the resonant layer excitation signal frequencies F1 to F2. n The excitation of the detector material induces nuclear magnetic resonance at a specified resonance layer, and the nuclear magnetic induction signals of all resonance layers are collected to obtain NMR1 to NMR2. n .

[0167] Excitation coils and induction coils can be used independently or in a shared manner.

[0168] 2.8 Irradiation layer

[0169] Based on the aforementioned basic scheme, the present invention is specifically implemented in one or more combinations of the following.

[0170] The M3000 process also includes:

[0171] M3100 steps:

[0172] Excitation light includes, but is not limited to, a beam of light of a specific wavelength that is focused or collimated to the irradiation point of the object being detected.

[0173] Scattered light is a beam of light that is scattered when the excitation light shines on the irradiation point of the object being detected. It includes, but is not limited to, Stokes scattering, anti-Stokes scattering, Brillouin scattering, Rayleigh scattering, and fluorescence.

[0174] The scattered light signal includes, but is not limited to, magnetization, resonance, and relaxation spectra detected in the magnetization, resonance, and relaxation states under nuclear magnetic resonance conditions, as well as non-magnetic spectra detected in the non-magnetic state. The spectral data includes at least the wavelength and intensity of the light.

[0175] The optical axis of the excitation light and the optical axis of the scattered light include, but are not limited to, coaxial or off-axis configurations.

[0176] M3200 Step: The maximum irradiation depth is defined as the depth that the excitation light can reach when it irradiates the object being tested. The thickness of the resonant layer and the scattered light parameters are adjusted so that the maximum irradiation depth is greater than or equal to two resonant layer thicknesses.

[0177] M3300 Steps: Divide the irradiation depth into one or more irradiation layers of equal thickness, denoted as L. m Where m is the maximum number of irradiation layers, DL is the thickness of the irradiation layer on the X-axis, and includes DL≥DR, m≥n≥2.

[0178] M3400 steps: Turn off the excitation signal of the resonance layer, irradiate the sample with excitation light, collect the scattered light signal, and calculate the characteristic peak signal of the decomposition spectrum based on the molecular bonds to be decomposed.

[0179] M3500 steps: Based on the maximum irradiation depth, calculate the number of covered resonance layers and the frequency of the corresponding resonance layer excitation signal. Sequentially excite the covered resonance layers to generate nuclear magnetic resonance. At the same time, collect the resonance layer nuclear magnetic induction signal and the scattered light signal of each layer. Based on the molecular bonds that need to be decomposed, decompose the characteristic peak signal layer by layer and calculate the layer-by-layer nuclear magnetic resonance signal and the layer-by-layer characteristic peak signal.

[0180] 2.9 Epidermis and Subcutaneous Layer

[0181] Based on the aforementioned basic solution, the present invention specifically includes, but is not limited to, one or more combinations of the following:

[0182] S5000 steps, including but not limited to:

[0183] M5100 steps: Divide the analyte into an epidermal layer and a subcutaneous layer. The epidermal layer includes, but is not limited to, the first irradiated layer or several irradiated layers connected to the first irradiated layer. Based on the magnetization characteristic peak signal, layer-by-layer nuclear magnetic resonance signal, and layer-by-layer characteristic peak signal of the epidermal layer, calculate the nuclear magnetic resonance signal and characteristic peak signal of the epidermal layer, and calculate the content of specific molecules in the analyte in the epidermal layer.

[0184] M5200 steps: Based on the magnetization characteristic peak signal, layer-by-layer nuclear magnetic resonance signal, and layer-by-layer characteristic peak signal of the subcutaneous layer, calculate the nuclear magnetic resonance signal and characteristic peak signal of the epidermal layer, and calculate the content of specific molecules in the subcutaneous layer of the detected substance.

[0185] M5300 Steps: Based on the surface shape and thickness of the resonance layer in the vertical direction and the X-axis, set the surface shape of the object to be detected to be consistent with the surface shape of the resonance layer, and set the epidermal thickness of the object to be less than the thickness of the resonance layer. The objects to be detected include human fingers, palms, arms, toes, feet, legs, soft-packaged liquids, and soft-packaged pharmaceuticals.

[0186] 2.10. Monitor blood glucose, hormones, and skin pigmentation.

[0187] Based on the aforementioned basic solution, the present invention specifically includes, but is not limited to, one or more combinations of the following, and also includes step S6000, specifically including, but not limited to:

[0188] M6100 Procedure: Human blood glucose testing, including but not limited to:

[0189] M6110 Procedure: Based on C6H 12 The structure of glucose molecules and the composition of their molecular bonds in O6 were determined using a Raman spectrometer with an excitation wavelength in the infrared band. Step M3100 was performed, and an aqueous solution with a known glucose concentration was prepared as the analyte. The scattered light of the analyte was measured to obtain spectral data.

[0190] M6120 Step: Based on the spectral data, decompose the characteristic peak signal and calculate the glucose concentration of the analyte to obtain the calculated concentration.

[0191] M6130 step: Compare the known concentration with the calculated concentration, then execute M4100 step to obtain empirical data.

[0192] M6140 Procedure: Based on C6H 12 The structure of glucose molecules and the composition of their molecular bonds in O6 were determined using a Raman spectrometer with an excitation wavelength in the infrared band. Step M3100 was performed, with the fingertip of a volunteer as the analyte. The scattered light of the analyte was measured to obtain spectral data. At the same time, blood glucose data from the volunteer was measured using a metrology-grade human blood glucose monitoring device as a known concentration.

[0193] M6150 Steps: Based on the spectral data, decompose the characteristic peak signals and calculate the glucose concentration of the analyte to obtain the calculated concentration.

[0194] M6160 step: Compare the known concentration with the calculated concentration, execute M4100 step, obtain empirical data, and obtain the content of glucose molecules in human blood.

[0195] M6170 step: Perform step M4200, or step M4300, to obtain the glucose molecule content in the blood.

[0196] M6200 Procedure: Human progesterone testing, including but not limited to:

[0197] M6210 steps: C6H 12 Replace O6 glucose with C 21 H 30 O2 progesterone, perform the M6100 step to obtain empirical data, and obtain the content of progesterone molecules in the blood.

[0198] M6220 step: Perform step M4200, or step M4300, to obtain the level of progesterone molecules in the blood.

[0199] M6300 procedure: Skin pigmentation detection, including but not limited to:

[0200] M6310 steps: Obtain the pigment molecular structure of skin pigment and collect the characteristic peak signals of the pigment molecular structure.

[0201] M6320 steps: Calculate the excitation signals of all resonance layers included in the skin layer, and sequentially use all resonance layer excitation signals to collect the resonance layer magnetic induction signals of all resonance layers.

[0202] M6330 step: Perform steps M4100, M4200, or M4300 to obtain the pigment content in the skin.

[0203] 2.11 Other Calculations

[0204] For specific molecules in the analyte, the method provided by this invention can also be used to detect other molecules in human blood and tissue fluid, including but not limited to those for detecting specific molecules in the analyte.

[0205] 2.12 Beneficial Effects of the Invention

[0206] (1) By adjusting the position of the magnet to obtain the gradient magnetic field, the composition of the gradient magnetic field is simplified to the maximum extent, the manufacturing cost is reduced to the maximum extent, and the volume is reduced to the maximum extent.

[0207] (2) The nuclear magnetic resonance mechanism is used to collect nuclear magnetic resonance signals in layers and the characteristic peak signals collected by the excitation light / scattered light spectrum are used. In the magnetized state, nuclear magnetic resonance state and relaxation state, the quantum magneto-optical sensing algorithm is used to realize the layer detection of specific molecules and calculate the content of specific molecules in layers.

[0208] (3) Based on the layered detection and calculation of the content of specific molecules, non-invasive in vitro diagnosis of human body can be achieved.

[0209] (4) The invention has achieved its purpose, intent and contribution. Attached Figure Description

[0210] List of attached diagrams and detailed descriptions:

[0211] Figure 1 System Overview Diagram

[0212] Figure 1 In the diagram, point O is the origin of the coordinate system, X / B is the X-axis and the one-dimensional gradient magnetic field axis, Z / W is the Z-axis and the gradient magnetic field width axis, N is the north pole of the magnet, and S is the south pole of the magnet.

[0213] Figure 2 Gradient magnetic field system diagram

[0214] Figure 2 In the diagram, 2001 is the X-axis, perpendicular to the direction of the main magnetic field generated by the magnet. 2002 is the Z-axis, parallel to the direction of the main magnetic field generated by the magnet. 2003 is the intersection of the X-axis and Z-axis. 2004 represents the gradient magnetic field. It's important to note that the multiple dashed lines indicated by 2004 represent lines of equal magnetic field strength, not lines indicating the direction of the magnetic field. Furthermore, according to... Figure 2 The magnets are arranged such that the lines of equal magnetic field strength gradually decrease from left to right, creating a gradient decreasing magnetic field from left to right. 2005 represents the magnetic moment, which is the magnetic moment of the atomic nucleus containing a specific proton in the material. Each magnetic moment is a representation of a point in time. 1 H is a hydrogen proton. 2006 is the excitation light, which is the excitation light that illuminates the analyte. 2007 is the irradiation region generated by the excitation light; depending on the molecular structure of the analyte, the excitation light can penetrate to different depths within the analyte. 2008 is the scattered light, which is the scattered light generated when excitation light photons strike the molecular bonds and atoms of the analyte. Although this mode also includes reflected light with the same wavelength as the excitation light, this invention application does not consider reflected light, but only considers scattered light with a wavelength different from the excitation light.

[0215] Figure 3 : Magnetic field distribution diagram of a parallel magnet

[0216] Figure 3In the diagram, a pair of magnets are arranged in a parallel configuration. According to the principle of magnetic field distribution, the magnetic field strength is non-uniform on both sides of the magnets, while the magnetic field strength in the middle region is uniform. Here, 3001 represents the X / B axis, 3002 the Z / W axis, 3003 the magnet itself, 3004 the magnetic moment, 3005 the uniform magnetic field region, and 3006 the non-uniform magnetic field region surrounding the magnets.

[0217] Figure 4 : Magnetic field distribution diagram of an inclined magnet

[0218] Figure 4 In the diagram, a pair of magnets are arranged at an angle along the X / B axis. Because the distance between the magnets' poles gradually changes, according to the principle of magnetic field distribution, the magnetic field strength along the X / B axis will also gradually change, resulting in a gradient magnetic field. Here, 4001 represents the X / B axis, 4002 the Z / W axis, 4003 the magnet, 4004 the magnetic moment, and 4005 the isostatic lines representing the gradient magnetic field.

[0219] Figure 5 Natural gradient magnetic field distribution map

[0220] Figure 5 In the middle, is Figure 4 This diagram illustrates the distribution of the natural gradient magnetic field formed by tilted magnets. 5001 represents the X / B axis, 5002 the Z / W axis, 5003 a schematic diagram of the distribution of isostatic magnetic field lines, and 5004 the magnetic moment. It's important to note that the magnetic field directions are arranged according to the magnetic moment direction, i.e., along the Z-axis, and the lines in 5003 represent lines indicating equal magnetic field strength.

[0221] Figure 6 One-dimensional gradient magnetic field function graph

[0222] Figure 6 In the diagram, 6001 is the X-axis of the gradient magnetic field, 6002 is the B-axis of the magnetic field strength, 6003 is the magnetic field strength line, and 6004 is the magnetic moment on the X-axis. Figure 6 As can be seen, starting from the origin O, the magnetic field strength gradually decreases along the X-axis to the right. Therefore, the X-axis is a schematic diagram of the formation of the gradient magnetic field.

[0223] Figure 7 Temperature function graph of permanent magnet

[0224] Figure 7 In this context, 7001 is the Kelvin temperature scale, 7002 is the rate of change of magnetic field strength, and 7003 is the rate of change of the magnetic field strength generated by a permanent magnet at different temperatures.

[0225] Figure 8 Polarizability temperature function graph

[0226] Figure 8 This is a curve showing the polarizability of nucleons against temperature in quantum mechanics. The 8001 Kelvin temperature axis represents the polarizability of the magnetic moment formed by the nucleon under the magnetization of the ambient magnetic field at the corresponding temperature, and the 8003 Kelvin curve represents the polarizability itself. It can be seen that at absolute zero, the polarizability of nucleons is 100%. As the temperature increases, the polarizability decreases exponentially. At room temperature, around 300 K, the polarizability is approximately -6 orders of magnitude. It is important to note that in this invention, in the quantum magneto-optical correlation function, the lower the temperature, the higher the degree of correlation.

[0227] Figure 9 Schematic diagram of glucose characteristic peaks

[0228] Figure 9 This is a schematic diagram of the characteristic peaks of glucose molecules based on Raman scattering spectrum (Stokes scattering and anti-Stokes scattering). In the diagram, 9010 is the frequency axis of the Raman spectrum, 9020 is the amplitude axis of the Raman spectrum, and 9001, 9002, and 9003 are the positions of several characteristic peaks of the glucose molecule.

[0229] Figure 10 Schematic diagram of the difference algorithm

[0230] Figure 10 In the diagram, 10010 represents the scattered light frequency axis of the Raman spectrum, 10020 represents the nonlinear amplitude axis of the Raman spectrum, and 10030 represents the position of a characteristic peak of the glucose molecule. A001 represents the total scattered light signal, and A002, A003, A004, and A005 represent the scattered light signals of several resonance and illumination layers. It is important to note that, for ease of plotting, the 10020 axis is nonlinear. The signal intensity at A001 is the sum of the signal intensity of each subsequent layer. For example, at the characteristic peak at 10030, the characteristic peak values ​​of each layer conform to the following formula:

[0231] A001 = A002 + A003 + A004 + A005

[0232] For the subcutaneous layer that needs to be tested, the characteristic peak curve can be referenced to A005. For example, at the characteristic peak of 1125, the point where A005 and 1125 intersect is the specific value of the characteristic peak at 1125 in the subcutaneous layer.

[0233] Figure 11 General In Vitro Diagnostic Product System Diagram

[0234] Figure 11This is an embodiment of a general in vitro diagnostic product system. 11001 is an inclined magnet, 11002 is a detection chamber for placing the analyte, 11003 is a temperature controller (e.g., a cooler), 11004 is a temperature sensor, and 11005 is a magnetic field sensor. Together with the spectral detection module and the control module, they realize the functions of a general in vitro diagnostic product. Detailed implementation method:

[0235] The objectives, intentions, and contributions of this invention are achieved through the technical solutions of the following two embodiments. It should be particularly noted that each specific embodiment has a specific use and industrial applicability, and requires basic knowledge in the industry to support its application beyond the claims. Therefore, any of the following embodiments does not encompass all the features and steps of this invention, nor is it a limitation thereof. The description in the claims is a core summary of the invention.

[0236] Example 1: General In Vitro Diagnostic Products

[0237] 1. Introduction and Illustrations

[0238] This embodiment is a system diagram of a general in vitro diagnostic product (IVD) of the present invention. It can detect the content distribution of specific molecules in the subcutaneous layer. The thickness dimensions of the skin layer and subcutaneous layer can be defined and adjusted.

[0239] For views, references Figures 1 to 11 .

[0240] 2. Plan and Steps

[0241] 2.1 Basic Structure

[0242] This invention, as a method for detecting the layered magnetic field of a natural gradient in quantum magneto-optical sensing, includes the following steps:

[0243] M1000 Steps: Set the magnet position to create a natural gradient magnetic field, and obtain the position function between the position and the magnetic field strength in the natural gradient magnetic field.

[0244] This includes, but is not limited to, placing a specific proton that can undergo nuclear magnetic resonance in a natural gradient magnetic field, dividing the detector into one or more resonance layers along the direction perpendicular to the natural gradient magnetic field from the outside to the inside, using the resonance layer excitation signal to excite the specific protons in the corresponding resonance layer of the detector to generate nuclear magnetic resonance, and collecting the nuclear magnetic induction signal of the resonance layer through an induction coil.

[0245] M3000 steps: The detector is irradiated from the outside with excitation light, the scattered light signal is collected, and the characteristic peak signal of the molecular bond of a specific proton in a specific molecule, including but not limited to, is decomposed in the scattered light signal.

[0246] M4000 step: A quantum magneto-optical sensing algorithm, which uses the resonant layer nuclear magnetic induction signal and the characteristic peak signal as independent variables, is used to calculate the content of specific molecules in the detected substance.

[0247] Typically, the most effective proton for detection in nuclear magnetic resonance (NMR) is the hydrogen proton. Therefore, as a special case, this patent will use the hydrogen proton (… 1 H) is the primary proton detected by NMR, but this does not exclude other protons, such as... 13 C 15 N、 19 F, 29 Si、 7 Li, 9 Be, etc. Specific molecules are compound molecules including, but not limited to, those with specific protons, such as glucose (C6H2O). 12 O6), or sodium chloride (NaCl) or progesterone (C 21 H 30 O2), etc.

[0248] In fact, based on the basic principles of this invention, this sensing method is a general method for non-invasive subcutaneous broad-spectrum IVD for living organisms.

[0249] 2.2 Quantum Magneto-optic Sensing Algorithm

[0250] Based on the aforementioned basic solution, the present invention specifically includes, but is not limited to, one or more combinations of the following:

[0251] Quantum magneto-optical sensing algorithms include, but are not limited to, empirical difference algorithms, correlation difference algorithms, or joint verification algorithms, specifically including:

[0252] M4100 steps: Empirical Differential Algorithm, specifically including but not limited to:

[0253] Based on the characteristic peak signal and the nuclear magnetic resonance induction signal of one or more resonance layers, the maximum depth that can be reached when the excitation light irradiates the analyte is used to divide one or more irradiation layers from the outside to the inside along the direction perpendicular to the natural gradient magnetic field. The irradiation layers include, but are not limited to, one or more resonance layers. Based on the empirical data of the analyte, the characteristic peak signal of the irradiation layer is decomposed and calculated, and the content of specific molecules in the analyte is calculated based on the nuclear magnetic resonance induction signal of the resonance layer and the characteristic peak signal of the irradiation layer.

[0254] Empirical data includes, but is not limited to, historical data obtained through testing, corresponding to the relationship between the NMR signal data of the irradiated layer and the resonance layer, the characteristic peak signal data of the irradiated layer, and the content data of specific molecules in the analyte.

[0255] Here, during the development of equipment, one common practice is to use a device with higher measurement accuracy as a calibration device, performing clinical calibration for each specific molecule to calibrate empirical data. Another feasible approach is to use artificial intelligence methods to obtain calibrated empirical data when a large amount of clinical data has been obtained.

[0256] The advantage of the empirical difference algorithm is that it uses a large amount of clinical data and can obtain relatively simple calculations.

[0257] M4200 steps: Correlation difference algorithm, including but not limited to:

[0258] Based on the characteristic peak signal and the nuclear magnetic resonance induction signal of one or more resonance layers, using the maximum depth that can be reached when the excitation light irradiates the detector, one or more irradiation layers are divided from the outside to the inside along the direction perpendicular to the natural gradient magnetic field. The irradiation layer includes one or more resonance layers. Based on the correlation function of the change of characteristic peak signal of specific protons included in specific molecules in the detector due to magnetization and nuclear magnetic resonance, the characteristic peak signal of the irradiation layer is decomposed and calculated. The content of specific molecules in the detector is calculated based on the nuclear magnetic resonance induction signal of the resonance layer and the characteristic peak signal of the irradiation layer.

[0259] The calculation of the correlation function includes, but is not limited to, one or a combination of the following methods:

[0260] Based on methods including but not limited to Rayleigh equations and probability calculations, the characteristic peak signals of the irradiated layer are decomposed and calculated.

[0261] Based on cloud-based statistical methods using artificial intelligence and big data, the characteristic peak signals of the irradiation layer are decomposed and calculated.

[0262] Based on methods including but not limited to the integration of artificial intelligence system plug-ins, the characteristic peak signals of the irradiation layer are decomposed and calculated.

[0263] Based on training with a multimodal large language model using artificial intelligence, the characteristic peak signal of the illumination layer is decomposed and calculated.

[0264] Based on, but not limited to, the physical state of the detected substance, such as solid, liquid, gas, and crystalline states, the characteristic peak signal of the irradiated layer is decomposed and calculated.

[0265] Based on factors including but not limited to the temperature, concentration, molecular structure, and types of mixed substances of the analyte, the characteristic peak signals of the irradiated layer are decomposed and calculated.

[0266] in accordance with Figure 8 It can be seen that as the temperature of the analyte decreases, specific nuclei (e.g., 1 The polarizability of H increases rapidly, while the polarizability of specific nucleons decreases rapidly with increasing temperature. When the polarizability is high, the number of nucleons involved in polarization is greater, resulting in more nuclei being affected by polarization during light scattering. This increases the influence on the frequency and emission angle of the scattered photons. Therefore, the lower the temperature, the greater the influence of polarization on the scattered light, and the degree of influence is related to... Figure 8 The polarizability curve is proportional to the polarizability curve.

[0267] The advantage of the correlation difference algorithm is that it can perform difference calculations accurately.

[0268] M4300 steps: Joint verification algorithm, including but not limited to:

[0269] Simultaneously, empirical difference algorithm and correlation difference algorithm are used to calculate the characteristic peak signal of the irradiated layer and the content of specific molecules in the detector, respectively.

[0270] Based on the joint verification function, the content of characteristic molecules in the analyte is calculated.

[0271] The calculation of the joint check function also includes, but is not limited to, one or a combination of the following methods:

[0272] Based on the weight parameters of the set empirical difference algorithm and correlation difference algorithm, the content of specific molecules in the detected substance is calculated by jointly verifying each characteristic peak.

[0273] Based on the theoretical parameters of the empirical difference algorithm and the correlation difference algorithm, the content of specific molecules in the analyte is calculated by jointly verifying each characteristic peak.

[0274] Based on the temperature of the analyte, the various characteristic peaks are jointly verified, and the content of specific molecules in the analyte is calculated.

[0275] Based on the concentration of the analyte, the various characteristic peaks are jointly verified, and the content of specific molecules in the analyte is calculated.

[0276] Based on the concentration and speciation of the analyte, the content of specific molecules in the analyte is calculated by jointly verifying each characteristic peak.

[0277] Combining empirical difference algorithms and correlation difference algorithms leverages the advantages of both, resulting in more accurate difference calculations. Industry professionals need to choose the appropriate algorithm based on the type of analyte and specific molecule being detected.

[0278] 2.3 Bar magnet, position and coordinate system

[0279] Based on the aforementioned basic solution, preferably, the present invention is implemented in one or more combinations of the following:

[0280] The M1000 process specifically includes:

[0281] M1110 Procedure: The magnets are composed of pairs of bar-shaped rectangular hexagonal permanent magnets, electromagnets, or superconducting magnets. Each pair of magnets consists of two magnets with a uniform magnetic field. The N pole of one magnet and the S pole of the other magnet are arranged face to face. The edges of the N pole magnet and the S pole magnet form a plane with the X-axis. The two edges are symmetrically distributed on both sides of the X-axis and intersect the X-axis at the origin. The angles between the two edges and the X-axis are both greater than 0 degrees and are equal. The position of the object to be detected on the X-axis is the location point. Excitation coils and induction coils are arranged according to the requirements of nuclear magnetic resonance.

[0282] M1120 Step: Establish a one-dimensional coordinate system along the X-axis using a pair or more magnets. By adjusting the position of the magnets, the magnitude of the magnetic field generated between the magnets moves along the X-axis, presenting a gradually increasing or decreasing one-dimensional gradient magnetic field.

[0283] M1130 Step: Using the direction of the magnetic field naturally generated between a pair or more magnets as the Z-axis direction, arrange the Z-axis perpendicular to the X-axis to establish a two-dimensional coordinate system of X-axis and Z-axis. By adjusting the position of the magnets, the magnitude of the magnetic field generated between the magnets is made to move along the X-axis and along the Z-axis, presenting a two-dimensional gradient magnetic field that gradually increases or decreases.

[0284] M1140 Step: Establish a three-dimensional coordinate system of X, Y, and Z, with the direction of the magnetic field naturally generated between a pair of magnets as the Z-axis and the direction perpendicular to both the X and Z axes as the Y-axis. By adjusting the position of the magnets, the magnitude of the magnetic field generated between the magnets is made to gradually increase or decrease along the X-axis, Z-axis, and Y-axis directions, presenting a three-dimensional gradient magnetic field.

[0285] As a bar magnet, it is a preferred option in this embodiment.

[0286] M1150 Steps: Adjust the position of the magnets, specifically including:

[0287] M1151 Step: Preferably, a pair of magnets are placed symmetrically about the X-axis, forming a natural gradient magnetic field between the angles formed by the pair of magnets.

[0288] M1152 Step: Preferably, multiple pairs of magnets are placed symmetrically about the X-axis, forming a natural gradient magnetic field between the angles formed by the multiple pairs of magnets.

[0289] M1153 Step: Preferably, a pair of magnets are placed symmetrically parallel to the X-axis, forming a natural gradient magnetic field at the entrance of the strip formed by the pair of magnets.

[0290] M1154 Step: Preferably, multiple pairs of magnets are placed symmetrically parallel to the X-axis to form a natural gradient magnetic field at the entrance of the long strip formed by the multiple pairs of magnets.

[0291] Regarding gradient magnetic fields, in some applications, it can be simplified to only one-dimensional detection. For example, for in vitro glucose detection in humans, only the X-axis gradient magnetic field is needed, and the Y-axis and Z-axis gradient magnetic fields are not required. Only layered detection is needed.

[0292] In fact, based on the latest inventions in permanent magnets in the industry, a high-strength neodymium iron boron permanent magnet is more suitable for the application of this invention. Furthermore, with the advancement of high-temperature superconductors, magnets constructed using inexpensive high-temperature superconductors will also be incorporated into the application of this invention.

[0293] For in vitro glucose detection in humans, it is important to locate the skin layer during layer detection and calculate the thickness of the X-axis gradient magnetic field based on the skin thickness. In subsequent calculations, the fingerprint spectral signal of glucose molecules in the skin layer should be removed, and only the glucose content in the subcutaneous tissue needs to be calculated.

[0294] The reason for numbering the gradient magnetic field is that in scattered light spectroscopy detection, the excitation light usually irradiates the detection object (such as the skin of the fingertip of a human finger) to a limited depth. For NMR-compatible layer detection, the depth of excitation light irradiation is usually a few millimeters, while the layer thickness of NMR is usually on the order of millimeters. Therefore, when correlating scattered light spectroscopy and NMR spectra, the number of layers is usually around two or three.

[0295] As a special case, 0-dimensional detection actually treats the entire object to be detected as a whole, without layering, striping, or dividing it into positions.

[0296] The selection of a calibration substance is primarily for the purpose of creating standard measuring weights during the initial application of this invention. A series of standards with known concentration gradients can be prepared in advance, tested, and recorded as standards for later applications. Here, the calibration substance can be an aqueous solution of a pure substance or other solutions.

[0297] Due to the influence of magnetic fields, specific protons in a magnetic field are magnetized by a static magnetic field, resonate due to an excited magnetic field, and experience attenuation during relaxation. Even in a non-magnetic state when the main magnetic field is turned off, the precession and nutation of specific protons differ, thus causing differences in the position and angle of the scattered light photons. Based on this, a set of equations relating the quantum motion of the nuclear magnetic resonance magnetic spectrum and the scattered light spectrum can be established for further solution.

[0298] For the parameters and calculations of nuclear magnetic resonance (NMR) and scattered light spectra, industry professionals should perform related calculations based on fundamental knowledge. For example, for subcutaneous tissue, the longitudinal relaxation time T1 and transverse relaxation time T2 in the NMR spectrum differ depending on the tissue type. For instance, when the magnetic field strength of the main magnetic field is 1.0T, for blood, T1 and T2 are 800ms and 180ms, respectively; for muscle, T1 and T2 are 600ms and 40ms, respectively; and for fat, T1 and T2 are 180ms and 90ms, respectively.

[0299] 2.4 Cylindrical magnet, position and coordinate system

[0300] Based on the aforementioned basic solution, preferably, the present invention is implemented in one or more combinations of the following:

[0301] The M1000 process also includes, but is not limited to:

[0302] M1210 Steps: The magnet is composed of a cylindrical permanent magnet, electromagnet, or superconducting magnet. The N and S poles of the magnet are arranged at both ends of the cylindrical body, and the diameters at both ends are different, forming a trapezoidal shape. The central axis of the cylindrical body is taken as the X-axis, and the position of the object to be detected on the X-axis is taken as the location point.

[0303] M1220 steps: Establish a one-dimensional coordinate system along the X-axis. By adjusting the position of the object being detected, the magnitude of the magnetic field is obtained by moving along the X-axis to present a gradually increasing or decreasing one-dimensional gradient magnetic field. The excitation coil and induction coil are arranged along the vertical direction of the X-axis.

[0304] M1230 steps: Establish a two-dimensional coordinate system with X and Z axes, arrange a Z gradient coil perpendicular to the X axis, generate a Z gradient magnetic field that gradually increases or decreases as it moves along the Z axis, and form a two-dimensional gradient magnetic field together with the X gradient magnetic field; and arrange excitation coil and induction coil.

[0305] M1240 steps: Establish a three-dimensional coordinate system of X, Y, and Z; arrange a Z gradient coil perpendicular to the X-axis and a Y gradient coil perpendicular to both the X and Z axes; generate a Z gradient magnetic field that gradually increases or decreases as it moves along the Z-axis through the Z gradient coil; and generate a Y gradient magnetic field that gradually increases or decreases as it moves along the Y-axis through the Y gradient coil; together with the X and Z gradient magnetic fields, they form a three-dimensional gradient magnetic field; and arrange excitation coils and induction coils.

[0306] Industry engineers should note that this type of cylindrical magnet has two ends with different diameters, the same wall thickness, and the magnetic poles are arranged at both ends. In this case, the X-axis inside the cylinder is parallel to the direction of the magnetic field, which is different from the direction of the magnetic field of a bar magnet.

[0307] Industry engineers can select these preferred options based on the properties of the analyte and specific molecules.

[0308] 2.5 Position Functions

[0309] Based on the aforementioned basic solution, preferably, the present invention is implemented in one or more combinations of the following:

[0310] The M1000 process also includes:

[0311] M1300 steps: Position functions include, but are not limited to:

[0312] M1310 steps: The position function includes, but is not limited to, the magnetic field strength at the X-axis position in a one-dimensional coordinate system of the natural gradient magnetic field, or the X-axis / Z-axis position in a two-dimensional coordinate system, or the X-axis / Z-axis / Y-axis position in a three-dimensional coordinate system.

[0313] M1320 Steps: The actual measurement method uses a magnetic field strength sensor to measure the position function at each location point in a natural gradient magnetic field of a specified environment.

[0314] M1330 Steps: The calculation method is based on the geometric relationship between the position of the magnet and the magnetic field strength. For each position point, the position function is calculated to obtain the position function.

[0315] As a one-dimensional coordinate system configuration, it includes, but is not limited to, detection of the surface of the object to be detected in the depth direction, such as subcutaneous detection of the fingertip.

[0316] As a two-dimensional coordinate system configuration, it includes, but is not limited to, moving the position of the excitation light / scattered light irradiation point to perform multi-point detection of the analyte, thereby achieving detection by avoiding capillaries and calculating the average of multiple points.

[0317] As a three-dimensional coordinate system configuration, it includes, but is not limited to, detection for completing three-dimensional imaging.

[0318] 2.6 Temperature Compensation

[0319] Based on the aforementioned basic solution, preferably, the present invention is implemented in one or more combinations of the following:

[0320] The M1000 process also includes:

[0321] M1410 Step: Use a temperature sensor to monitor the magnetic field temperature by means of cooling, heating or natural ambient temperature.

[0322] M1420 Step: Based on the magnetic field temperature, perform positive linear, negative linear, or nonlinear temperature compensation for the natural gradient magnetic field itself, according to the magnitude of the natural gradient magnetic field.

[0323] M1430 Steps: Use constant temperature control for the magnetic field temperature, and perform positive linear, negative linear, or nonlinear temperature compensation for the natural gradient magnetic field itself.

[0324] M1510 Step: Use a magnetic field sensor to obtain the measured magnetic field strength at the location point, and calculate the magnetic field deviation compensation for the natural gradient magnetic field based on the difference between the measured magnetic field strength and the set magnetic field strength at the location point.

[0325] In the quantum principle of nuclear magnetic resonance, the polarizability—the proportion of an atomic nucleus polarized by an external magnetic field—is an exponential function of temperature, such as... Figure 8 As shown. At absolute zero, the polarizability of nucleons is 100%. As temperature increases, the polarizability decreases exponentially; at room temperature, around 300 K, the polarizability is approximately -6 orders of magnitude. It is important to note that in this invention, the lower the temperature in the quantum magneto-optical correlation function, the higher the degree of correlation. Therefore, monitoring the temperature and achieving temperature compensation is crucial for improving the measurement accuracy of this invention. Designers in the field should be able to employ some well-known and commonly used temperature measurement and compensation techniques to achieve temperature compensation.

[0326] 2.7 Resonance Layer

[0327] Based on the aforementioned basic solution, the present invention specifically includes, but is not limited to, one or more combinations of the following:

[0328] The M2000 process also includes:

[0329] M2100 step: According to the position function, in the natural gradient magnetic field, connect one or more adjacent position points whose absolute difference in magnetic field strength is less than the layer error to form a resonant layer, and so on, in the natural gradient magnetic field, divide all position points into several resonant layers, wherein the difference in layer error on the X-axis is the thickness of the resonant layer.

[0330] M2200 steps: Based on the magnetic field strength of a resonance layer and the gyromagnetic ratio of a specific proton, calculate the frequency of the resonance layer excitation signal of that resonance layer, and calculate the frequency of the resonance layer excitation signal of all resonance layers.

[0331] M2300 steps: Starting from the origin, number all resonant layers and their corresponding excitation signals from 1, denote the largest resonant layer number as n, and calculate R1 to R2 for all resonant layers. n The frequencies of the excitation signals of the corresponding resonant layers are used to obtain F1 to F.n .

[0332] M2400 Steps: From the first resonant layer to the last resonant layer, sequentially use the resonant layer excitation signal frequencies F1 to F2. n The excitation of the detector material induces nuclear magnetic resonance at a specified resonance layer, and the nuclear magnetic induction signals of all resonance layers are collected to obtain NMR1 to NMR2. n .

[0333] Excitation coils and induction coils can be used independently or in a shared manner.

[0334] In addition to the one-dimensional method mentioned above, the resonant layer can also be set up by establishing two-dimensional and three-dimensional gradient magnetic fields and corresponding excitation coils and excitation signals, so as to complete the detection of two-dimensional rectangular strip resonance and three-dimensional cube (volumetric element).

[0335] In the field of nuclear magnetic resonance imaging (MRI), the detection zone is commonly referred to as a "volumetric element." The introduction of the detection zone is to further enhance the localization of the detection point. It is important to note that the detection point must correspond to the location of the detection zone; that is, the detection point must be located on the detection plane along the X-axis of the detection zone.

[0336] As a specific method for implementing bar scanning and detection bit scanning, this embodiment designs the excitation light generation module and the scattered light collection module into a fixed structure, and then designs a stepper motor controller that moves in a plane along the X and Y axes, so that the detection point can move with the position of the detection bar and the detection bit.

[0337] When there are scars or other interferences on the skin, the introduction of 3D detection can skip the scars or other interference areas, so that the detection point is located on normal skin or is aimed at the subcutaneous blood vessels for detection.

[0338] 2.8 Irradiation layer

[0339] Based on the aforementioned basic scheme, the present invention is specifically implemented in one or more combinations of the following.

[0340] The M3000 process also includes:

[0341] M3100 steps:

[0342] Excitation light includes, but is not limited to, a beam of light of a specific wavelength that is focused or collimated to the irradiation point of the object being detected.

[0343] Scattered light is a beam of light that is scattered when the excitation light shines on the irradiation point of the object being detected. It includes, but is not limited to, Stokes scattering, anti-Stokes scattering, Brillouin scattering, Rayleigh scattering, and fluorescence.

[0344] The scattered light signal includes, but is not limited to, magnetization, resonance, and relaxation spectra detected in the magnetization, resonance, and relaxation states under nuclear magnetic resonance conditions, as well as non-magnetic spectra detected in the non-magnetic state. The spectral data includes at least the wavelength and intensity of the light.

[0345] The optical axis of the excitation light and the optical axis of the scattered light include, but are not limited to, coaxial or off-axis configurations.

[0346] M3200 Step: The maximum irradiation depth is defined as the depth that the excitation light can reach when it irradiates the object being tested. The thickness of the resonant layer and the scattered light parameters are adjusted so that the maximum irradiation depth is greater than or equal to two resonant layer thicknesses.

[0347] M3300 Steps: Divide the irradiation depth into one or more irradiation layers of equal thickness, denoted as L. m Where m is the maximum number of irradiation layers, DL is the thickness of the irradiation layer on the X-axis, and includes DL≥DR, m≥n≥2.

[0348] M3400 steps: Turn off the excitation signal of the resonance layer, irradiate the sample with excitation light, collect the scattered light signal, and calculate the characteristic peak signal of the decomposition spectrum based on the molecular bonds to be decomposed.

[0349] M3500 steps: Based on the maximum irradiation depth, calculate the number of covered resonance layers and the frequency of the corresponding resonance layer excitation signal. Sequentially excite the covered resonance layers to generate nuclear magnetic resonance. At the same time, collect the resonance layer nuclear magnetic induction signal and the scattered light signal of each layer. Based on the molecular bonds that need to be decomposed, decompose the characteristic peak signal layer by layer and calculate the layer-by-layer nuclear magnetic resonance signal and the layer-by-layer characteristic peak signal.

[0350] Due to differences in the properties of the analyte, when the excitation light illuminates the detection point of the analyte, it can penetrate to a certain depth along the optical axis of the excitation light in a gradient-attenuated manner, depending on the wavelength of the excitation light and the properties of the analyte. When using infrared lasers with wavelengths of 785nm and 1064nm as excitation light, it can penetrate approximately 2mm to 3.5mm into human skin. At this depth, the excitation light will gradually attenuate with changes in depth. The resulting scattered light also gradually weakens with increasing depth. In this patent application, we will correct the scattered light intensity of the detection layer according to linear attenuation.

[0351] It is important to note that although there is a detection layer issue in nuclear magnetic resonance (NMR) under gradient magnetic field conditions, the depth of the detection layer must be compatible with the depth of the excitation light entering the object due to the limitation of the excitation light's penetration depth. Otherwise, it will be impossible to achieve a joint solution of the magnetic spectrum and the spectral spectrum.

[0352] It should be noted that for subcutaneous tissue detection that does not require imaging, only 1D layer detection is needed.

[0353] For the application of non-invasive in vitro glucose detection in humans, another step in the calibration process involves drawing venous blood from the human body and analyzing the resulting glucose value in a biochemical analyzer. This glucose value is used as the known glucose value of the calibrator. Simultaneously, the overall nuclear magnetic resonance (NMR) spectrum and surface scattering light spectrum data detected in this step are used as a reference, and the glucose value obtained from the biochemical analyzer is used as comparative data to calibrate the detection content calculated in this step, establishing a comparative database. Through multiple experiments with various glucose values, comparative data for the database are obtained.

[0354] For other subcutaneous molecular detections, such as glucose (C6H4O3), 12 O6), or sodium chloride (NaCl) or progesterone (C 21 H 30 For substances such as O2, the calibrator needs to be selected based on the standard content of progesterone, and a comparison database needs to be established for detection.

[0355] 2.9 Epidermis and Subcutaneous Layer

[0356] Based on the aforementioned basic solution, preferably, the present invention is implemented in one or more combinations of the following:

[0357] S5000 steps, including but not limited to:

[0358] M5100 steps: Divide the analyte into an epidermal layer and a subcutaneous layer. The epidermal layer includes, but is not limited to, the first irradiated layer or several irradiated layers connected to the first irradiated layer. Based on the magnetization characteristic peak signal, layer-by-layer nuclear magnetic resonance signal, and layer-by-layer characteristic peak signal of the epidermal layer, calculate the nuclear magnetic resonance signal and characteristic peak signal of the epidermal layer, and calculate the content of specific molecules in the analyte in the epidermal layer.

[0359] M5200 steps: Based on the magnetization characteristic peak signal, layer-by-layer nuclear magnetic resonance signal, and layer-by-layer characteristic peak signal of the subcutaneous layer, calculate the nuclear magnetic resonance signal and characteristic peak signal of the epidermal layer, and calculate the content of specific molecules in the subcutaneous layer of the detected substance.

[0360] M5300 Steps: Based on the surface shape and thickness of the resonance layer in the vertical direction and the X-axis, set the surface shape of the object to be detected to be consistent with the surface shape of the resonance layer, and set the epidermal thickness of the object to be less than the thickness of the resonance layer. The objects to be detected include human fingers, palms, arms, toes, feet, legs, soft-packaged liquids, and soft-packaged pharmaceuticals.

[0361] Here, "one dimension" refers to dividing the entire object to be tested into several detection layers, and then performing further testing on each detection layer.

[0362] The calculation of the maximum number of detection layers is based on the depth to which the excitation light can penetrate the analyte (e.g., skin). For example, for a laser with a wavelength of 785nm, the maximum depth in the skin of a human fingertip is about 3.0mm, while the depth of the epidermis and dermis in the skin is about 1.2mm. For glucose detection, it needs to be performed in the subcutaneous tissue below the dermis. Therefore, it is necessary to calculate the nuclear magnetic spectrum and scattered light spectrum data of the detection layers from 1.2mm to 3.0mm. Specifically, during nuclear magnetic resonance (NMR) calculations in a gradient magnetic field, the volumetric size is determined. For example, if the volumetric size is 1.40 mm, then the thickness of the first volumetric layer is 1.4 mm, which corresponds to the epidermis and dermis. We do not need to detect glucose levels in this layer. The second volumetric layer, with a thickness between 1.4 mm and 2.8 mm, is precisely the location where we need to detect glucose. The excitation magnetic field frequency for this layer is calculated, and based on this frequency, the 1.4 mm to 2.8 mm tissue under the finger's skin is brought into a hydrogen NMR state. The scattered light spectrum obtained under this NMR state is then subtracted from the attenuation of the scattered light from the first layer (1.4 mm) to obtain the scattered light spectrum signal of this detection layer. Based on this, and by comparing with a database, the detection content of a specific molecule—glucose—is calculated.

[0363] 2.10. Monitor blood glucose, hormones, and skin pigmentation.

[0364] Based on the aforementioned basic solution, the present invention specifically includes, but is not limited to, one or more combinations of the following, and also includes step S6000, specifically including, but not limited to:

[0365] M6100 Procedure: Human blood glucose testing, including but not limited to:

[0366] M6110 Procedure: Based on C6H 12 The structure of glucose molecules and the composition of their molecular bonds in O6 were determined using a Raman spectrometer with an excitation wavelength in the infrared band. Step M3100 was performed, and an aqueous solution with a known glucose concentration was prepared as the analyte. The scattered light of the analyte was measured to obtain spectral data.

[0367] M6120 Step: Based on the spectral data, decompose the characteristic peak signal and calculate the glucose concentration of the analyte to obtain the calculated concentration.

[0368] M6130 step: Compare the known concentration with the calculated concentration, then execute M4100 step to obtain empirical data.

[0369] M6140 Procedure: Based on C6H 12The structure of glucose molecules and the composition of their molecular bonds in O6 were determined using a Raman spectrometer with an excitation wavelength in the infrared band. Step M3100 was performed, with the fingertip of a volunteer as the analyte. The scattered light of the analyte was measured to obtain spectral data. At the same time, a human blood glucose monitoring device with a metrological electrode was used to detect the blood glucose data of the volunteer as a known concentration.

[0370] M6150 Steps: Based on the spectral data, decompose the characteristic peak signals and calculate the glucose concentration of the analyte to obtain the calculated concentration.

[0371] M6160 step: Compare the known concentration with the calculated concentration, execute M4100 step, obtain empirical data, and obtain the content of glucose molecules in human blood.

[0372] M6170 step: Perform step M4200, or step M4300, to obtain the glucose molecule content in the blood.

[0373] M6200 Procedure: Human progesterone testing, including but not limited to:

[0374] M6210 steps: C6H 12 Replace O6 glucose with C 21 H 30 O2 progesterone, perform the M6100 step to obtain empirical data, and obtain the content of progesterone molecules in the blood.

[0375] M6220 step: Perform step M4200, or step M4300, to obtain the level of progesterone molecules in the blood.

[0376] M6300 procedure: Skin pigmentation detection, including but not limited to:

[0377] M6310 steps: Obtain the pigment molecular structure of skin pigment and collect the characteristic peak signals of the pigment molecular structure.

[0378] M6320 steps: Calculate the excitation signals of all resonance layers included in the skin layer, and sequentially use all resonance layer excitation signals to collect the resonance layer magnetic induction signals of all resonance layers.

[0379] M6330 step: Perform steps M4100, M4200, or M4300 to obtain the pigment content in the skin.

[0380] Blood glucose testing measures the glucose level in the blood. Similarly, progesterone testing measures the progesterone level in the blood and tissue fluid. This is crucial for diabetic patients and pregnant women. Furthermore, this invention can also be applied to the beauty industry to detect skin pigmentation.

[0381] A key objective of this invention is to achieve non-invasive detection on human skin without breaking the skin. One important embodiment of this invention provides a feasible and innovative method for non-invasive IVD.

[0382] 2.11 Other Calculations

[0383] Based on the aforementioned basic solution, preferably, the present invention is implemented in one or more combinations of the following:

[0384] For specific molecules in the analyte, the method provided by this invention can also be used to detect other molecules in human blood and tissue fluid, including but not limited to those in the analyte. It can also directly detect certain molecules on the skin epidermis, such as skin pigmentation in the beauty industry.

[0385] Example 2: Non-invasive in vitro blood glucose diagnostic (IVD) method

[0386] 1. Introduction

[0387] Unlike Example 1, this example is only a simple and portable design method for blood glucose IVD devices.

[0388] This is not intended as an example of imaging or performing in vitro detection in an image-based manner, but rather as a representation of a class of low-cost human IVD detection methods. Those skilled in the art should be able to construct a low-cost human IVD device based on this method, such as one for detecting glucose.

[0389] 2. Diagram Explanation

[0390] The overall structural diagram of this embodiment is shown below. Figure 11 Other illustrations are as described in Embodiment 1. It should be noted that these illustrations are merely one example of a structure and are not intended to limit the scope of this embodiment.

[0391] 3. Explanation of Differences

[0392] The similarities with Embodiment 1 will not be repeated here, as illustrated in the foregoing figures. The differences are as follows:

[0393] 1. Only one pair of bar-shaped permanent magnets are used, arranged at an angle, such as... Figure 4 As stated above.

[0394] 2. Only one-dimensional resonance layer-based nuclear magnetic resonance is used for preparation.

[0395] 3. The permanent magnets are made of highly magnetized neodymium iron boron magnets.

[0396] 4. For magnets, semiconductor diodes are used for cooling, and the temperature can be reduced to -100℃ to 30℃. At the same time, temperature compensation calculations are used.

[0397] 5. The excitation light wavelength is 785nm or 1064nm, and the spectrum is analyzed and collected using the Stokes scattering method.

[0398] 6. Figure 11 The components are designed into a miniaturized whole, which is used in conjunction with a high-precision Raman spectrometer.

[0399] 7. Alternatively, a small computer system and wireless communication can be used to design the system as a complete and independent portable IVD device.

Claims

1. A method for detecting the layered structure of a natural gradient magnetic field using quantum magneto-optical sensing, characterized in that, include: M1000 step: Set the position of the magnet to form a natural gradient magnetic field, and obtain the position function between the position and the magnetic field strength in the natural gradient magnetic field; M2000 steps: Place the detector containing specific protons capable of nuclear magnetic resonance in the natural gradient magnetic field, divide the detector into one or more resonance layers from the outside to the inside along the direction perpendicular to the natural gradient magnetic field, use the resonance layer excitation signal to excite the specific protons in the corresponding resonance layer of the detector to generate nuclear magnetic resonance through the excitation coil, and collect the nuclear magnetic induction signal of the resonance layer through the induction coil. M3000 steps: The excitation light is used to irradiate the sample from the outside, the scattered light signal is collected, and the characteristic peak signal of the molecular bond of the specific proton included in the specific molecule is decomposed in the scattered light signal; M4000 step: A quantum magneto-optical sensing algorithm, which uses the resonant layer nuclear magnetic induction signal and the characteristic peak signal as independent variables, is used to calculate the content of specific molecules in the detected substance.

2. The method according to claim 1, characterized in that, The quantum magneto-optical sensing algorithm includes empirical difference algorithm, correlation difference algorithm, or joint verification algorithm, specifically including: M4100 step: The empirical difference algorithm specifically includes: Based on the characteristic peak signal and the nuclear magnetic resonance induction signal of one or more resonance layers, and using the maximum depth that can be reached when the excitation light irradiates the detector, one or more irradiation layers are divided from the outside to the inside along the vertical direction of the natural gradient magnetic field, wherein the irradiation layer includes one or more resonance layers. Based on the empirical data of the detector, the characteristic peak signal of the irradiation layer is decomposed and calculated, and the content of a specific molecule in the detector is calculated based on the nuclear magnetic resonance induction signal of the resonance layer and the characteristic peak signal of the irradiation layer. Empirical data includes historical data on the correspondence between the NMR signal data of the irradiated layer and the resonance layer obtained through testing, the characteristic peak signal data of the irradiated layer, and the content data of specific molecules in the analyte. M4200 step: The correlation difference algorithm specifically includes: Based on the characteristic peak signal and the nuclear magnetic resonance induction signal of one or more resonance layers, using the maximum depth that can be reached when the excitation light irradiates the detector, one or more irradiation layers are divided from the outside to the inside along the direction perpendicular to the natural gradient magnetic field, wherein the irradiation layer includes one or more resonance layers. Based on the correlation function of the change of characteristic peak signal of specific protons included in specific molecules in the detector due to magnetization and nuclear magnetic resonance, the characteristic peak signal of the irradiation layer is decomposed and calculated, and the content of specific molecules in the detector is calculated based on the nuclear magnetic resonance induction signal of the resonance layer and the characteristic peak signal of the irradiation layer. The calculation of the correlation function also includes one or a combination of the following methods: Based on Rayleigh equations and probability calculation methods, the characteristic peak signals of the irradiated layer are decomposed and calculated; Based on cloud-based statistical methods using artificial intelligence and big data, the characteristic peak signals of the irradiation layer are decomposed and calculated; Based on the method of accessing the AI ​​system plug-in, the characteristic peak signal of the irradiation layer is decomposed and calculated; Based on training including a multimodal large language model using artificial intelligence, the characteristic peak signal of the illumination layer is decomposed and calculated; Based on the physical state of the detected substance, including solid, liquid, gas, and crystalline states, the characteristic peak signals of the irradiated layer are decomposed and calculated. Based on factors including the temperature, concentration, molecular structure, and types of mixed substances of the analyte, the characteristic peak signals of the irradiated layer are decomposed and calculated. M4300 Steps: The joint verification algorithm specifically includes: Simultaneously, the empirical difference algorithm and the correlation difference algorithm are used to calculate the characteristic peak signal of the irradiated layer and the content of specific molecules in the detector, respectively; The content of a specific molecule in the analyte is calculated based on the joint verification function; The calculation of the joint check function also includes one or a combination of the following methods: Based on the weight parameters of the empirical difference algorithm and the correlation difference algorithm, the characteristic peaks are jointly verified, and the content of specific molecules in the detectable is calculated. Based on the theoretical parameters of the empirical difference algorithm and the correlation difference algorithm, the content of specific molecules in the detectable is calculated by jointly verifying each characteristic peak. Based on the temperature of the analyte, the various characteristic peaks are jointly verified, and the content of specific molecules in the analyte is calculated. Based on the concentration of the analyte, the various characteristic peaks are jointly verified, and the content of specific molecules in the analyte is calculated. Based on the concentration and form of the analyte, the content of specific molecules in the analyte is calculated by jointly verifying each characteristic peak.

3. The method according to claim 2, characterized in that, The M1000 step specifically includes: M1110 Steps: The magnets are composed of pairs of bar-shaped rectangular hexagonal permanent magnets, electromagnets, or superconducting magnets. Each pair of magnets consists of two magnets with a uniform magnetic field. The N pole of one magnet and the S pole of the other magnet are arranged face to face. The edge of the N pole magnet and the edge of the S pole magnet form a plane with the X-axis. The two edge lines are symmetrically distributed on both sides of the X-axis and intersect the X-axis at the origin. The angles between the two edge lines and the X-axis are both greater than 0 degrees and are equal. The position of the object to be detected on the X-axis is the location point. Excitation coils and induction coils are arranged according to the requirements of nuclear magnetic resonance. M1120 Steps: Establish a one-dimensional coordinate system along the X-axis using a pair or more magnets. By adjusting the positions of the magnets, the magnitude of the magnetic field generated between them is shifted along the X-axis, resulting in a gradually increasing or decreasing one-dimensional gradient magnetic field; and / or, M1130 Step: Using the direction of the magnetic field naturally generated between a pair or more magnets as the Z-axis, arrange the Z-axis perpendicular to the X-axis to establish a two-dimensional coordinate system of X and Z axes. By adjusting the position of the magnets, the magnitude of the magnetic field generated between the magnets is made to gradually increase or decrease along the X-axis and Z-axis directions, presenting a two-dimensional gradient magnetic field; and / or, M1140 Step: Establish a three-dimensional coordinate system of X, Y, and Z, with the direction of the magnetic field naturally generated between a pair of magnets as the Z-axis and the direction perpendicular to both the X and Z axes as the Y-axis. By adjusting the position of the magnets, the magnitude of the magnetic field generated between the magnets is made to gradually increase or decrease along the X-axis, Z-axis, and Y-axis directions, presenting a three-dimensional gradient magnetic field.

4. The method according to claim 2, characterized in that, The M1000 step also includes: M1210 steps: The magnet is composed of a cylindrical permanent magnet, electromagnet, or superconducting magnet. The N pole and S pole of the magnet are arranged at both ends of the cylindrical body, and the diameters at both ends are different, forming a trapezoidal shape. The central axis of the cylindrical body is taken as the X-axis, and the position of the object to be detected on the X-axis is the location point. M1220 Steps: Establish a one-dimensional coordinate system along the X-axis; by adjusting the position of the object being detected, obtain a one-dimensional gradient magnetic field whose magnitude gradually increases or decreases as it moves along the X-axis; arrange the excitation coil and induction coil perpendicular to the X-axis; and / or, M1230 steps: Establish a two-dimensional coordinate system with X and Z axes; arrange a Z-gradient coil perpendicular to the X-axis; generate a Z-gradient magnetic field that gradually increases or decreases as it moves along the Z-axis, forming a two-dimensional gradient magnetic field together with the X-gradient magnetic field; and arrange excitation coils and induction coils; and / or, M1240 steps: Establish a three-dimensional coordinate system of X, Y, and Z, arrange a Z gradient coil perpendicular to the X-axis and a Y gradient coil perpendicular to both the X and Z axes. The Z gradient coil generates a gradually increasing or decreasing Z gradient magnetic field that moves along the Z-axis. The Y gradient coil generates a gradually increasing or decreasing Y gradient magnetic field that moves along the Y-axis. Together with the X and Z gradient magnetic fields, they form a three-dimensional gradient magnetic field. Excitation coils and induction coils are also arranged.

5. The method according to claim 3 or 4, characterized in that, The M1000 step also includes: M1300 step: The position function specifically includes: M1310 step: The position function includes the magnetic field strength at the X-axis position in the one-dimensional coordinate system, or the X-axis / Z-axis position in the two-dimensional coordinate system, or the X-axis / Z-axis / Y-axis position in the three-dimensional coordinate system of the natural gradient magnetic field. M1320 Step: The method involves actual measurement using a magnetic field strength sensor within the natural gradient magnetic field of a specified environment, at each location point, to obtain the position function; or... M1330 Step: The calculation method is to calculate the position function for each position point based on the geometric relationship between the position of the magnet and the magnetic field strength.

6. The method according to claim 5, characterized in that, The M1000 step also includes: M1410 Step: Use a temperature sensor to monitor the magnetic field temperature by means of cooling, heating, or ambient temperature. M1420 Step: Based on the magnetic field temperature, perform positive linear, negative linear, or nonlinear temperature compensation for the natural gradient magnetic field itself, according to the magnitude of the natural gradient magnetic field; and / or, M1430 Step: Using a constant-temperature control system for the magnetic field temperature, perform positive linear, negative linear, or nonlinear temperature compensation for the natural gradient magnetic field itself; and / or, M1510 Step: Use a magnetic field sensor to obtain the measured magnetic field strength at the location point, and calculate the magnetic field deviation compensation of the natural gradient magnetic field based on the difference between the measured magnetic field strength and the set magnetic field strength at the location point.

7. The method according to claim 5, characterized in that, The M2000 step also includes: M2100 step: According to the position function, in the natural gradient magnetic field, connect one or more adjacent position points whose absolute difference in magnetic field strength is less than the layer error to form a resonant layer, and so on, in the natural gradient magnetic field, divide all position points into several resonant layers, wherein the difference in layer error on the X-axis is the thickness of the resonant layer. M2200 steps: Based on the magnetic field strength of a resonance layer and the gyromagnetic ratio of a specific proton, calculate the frequency of the resonance layer excitation signal of that resonance layer, and calculate the frequency of the resonance layer excitation signal of all resonance layers; M2300 steps: Starting from the origin, number all resonant layers and their corresponding excitation signals from 1, denote the largest resonant layer number as n, and calculate R1 to R2 for all resonant layers. n The frequencies of the excitation signals of the corresponding resonant layers are used to obtain F1 to F. n ; M2400 Steps: From the first resonant layer to the last resonant layer, sequentially use the resonant layer excitation signal frequencies F1 to F2. n The excitation of the detector material induces nuclear magnetic resonance at a specified resonance layer, and the nuclear magnetic induction signals of all resonance layers are collected to obtain NMR1 to NMR2. n ; Excitation coils and induction coils can be used independently or in a shared manner.

8. The method according to claim 2 or 7, characterized in that, The M3000 step also includes: M3100 steps: Excitation light consists of a beam of light of a specific wavelength that is focused or collimated and directed onto the irradiation point of the object being detected. Scattered light is a beam of light scattered by the excitation light hitting the irradiation point of the detector. It includes Stokes scattering, anti-Stokes scattering, Brillouin scattering, Rayleigh scattering, and fluorescence. The scattered light signal also includes magnetization, resonance, and relaxation spectra detected in the nuclear magnetic resonance state, as well as non-magnetic spectra detected in the non-magnetic state. The spectral data includes at least the wavelength and intensity of the light. The optical axis of the excitation light and the optical axis of the scattered light can be coaxial or non-axial. M3200 steps: The maximum irradiation depth is defined as the depth that the excitation light can reach when it irradiates the object to be detected. Adjust the resonant layer thickness and scattered light parameters so that the maximum irradiation depth is greater than or equal to 2 resonant layer thicknesses. M3300 Steps: Divide the irradiation depth into one or more irradiation layers of equal thickness, denoted as L. m Where m is the maximum number of irradiation layers, DL is the thickness of the irradiation layer on the X-axis, and includes DL≥DR, m≥n≥2; M3400 steps: Turn off the excitation signal of the resonance layer, irradiate the detector with excitation light, collect the scattered light signal, and calculate the characteristic peak signal of the decomposed spectrum based on the molecular bonds to be decomposed. M3500 steps: Based on the maximum irradiation depth, calculate the number of covered resonance layers and the frequency of the corresponding resonance layer excitation signal. Sequentially excite the covered resonance layers to generate nuclear magnetic resonance. At the same time, collect the resonance layer nuclear magnetic induction signal and the scattered light signal of each layer. Based on the molecular bonds that need to be decomposed, decompose the characteristic peak signal layer by layer and calculate the layer-by-layer nuclear magnetic resonance signal and the layer-by-layer characteristic peak signal.

9. The method according to claim 8, characterized in that, The M5000 steps specifically include: M5100 steps: Divide the analyte into an epidermal layer and a subcutaneous layer. The epidermal layer includes a first irradiated layer or several irradiated layers connected to the first irradiated layer. Based on the magnetization characteristic peak signal, layer-by-layer NMR signal, and layer-by-layer characteristic peak signal of the epidermal layer, calculate the NMR signal and characteristic peak signal of the epidermal layer, and calculate the content of specific molecules in the analyte in the epidermal layer; and / or, M5200 steps: Divide the analyte into an epidermal layer and a subcutaneous layer. The epidermal layer includes a first irradiated layer or several irradiated layers connected to the first irradiated layer. Based on the magnetization characteristic peak signal, layer-by-layer nuclear magnetic resonance signal, and layer-by-layer characteristic peak signal of the subcutaneous layer, calculate the nuclear magnetic resonance signal and characteristic peak signal under the epidermal layer, and calculate the content of specific molecules in the analyte in the subcutaneous layer. M5300 Steps: Based on the surface shape and thickness of the resonance layer in the vertical direction and the X-axis, set the surface shape of the object to be detected to be consistent with the surface shape of the resonance layer, and set the epidermal thickness of the object to be less than the thickness of the resonance layer. The objects to be detected include human fingers, palms, arms, toes, feet, legs, soft-packaged liquids, and soft-packaged pharmaceuticals.

10. The method according to claim 9, characterized in that, The M6000 procedure specifically includes: M6100 Procedure: Human Blood Glucose Testing, specifically including: M6110 Procedure: Based on C6H 12 The structure of glucose molecules and the composition of their molecular bonds in O6 were determined using a Raman spectrometer with an excitation wavelength in the infrared band. Step M3100 was performed, and an aqueous solution with a known glucose concentration was prepared as the analyte. The scattered light of the analyte was measured to obtain spectral data. M6120 Step: Based on the spectral data, decompose the characteristic peak signals and calculate the glucose concentration of the analyte to obtain the calculated concentration; M6130 step: Compare the known concentration with the calculated concentration, perform M4100 step to obtain empirical data; and / or, M6140 Procedure: Based on C6H 12 The structure of glucose molecules and the composition of their molecular bonds in O6 were determined using a Raman spectrometer with an excitation wavelength in the infrared band. Step M3100 was performed, with the fingertip of a volunteer as the analyte. The scattered light of the analyte was measured to obtain spectral data. At the same time, blood glucose data from the volunteer was detected using a metrology-grade human blood glucose monitoring device as a known concentration. M6150 steps: Based on the spectral data, decompose the characteristic peak signals and calculate the glucose concentration of the analyte to obtain the calculated concentration; M6160 step: Compare the known concentration with the calculated concentration, execute M4100 step, obtain empirical data, and obtain the content of glucose molecules in human blood; M6170 step: Perform step M4200, or perform step M4300, to obtain the glucose molecule content in the blood; M6200 Procedure: Human Progesterone Testing, specifically including: M6210 Steps: C6H 12 Replace O6 glucose with C 21 H 30 O2 progesterone, perform the M6100 step to obtain empirical data, and obtain the content of progesterone molecules in the blood; M6220 step: Perform step M4200, or perform step M4300, to obtain the level of progesterone molecules in the blood; M6300 procedure: Skin pigmentation test, specifically including: M6310 steps: Obtain the pigment molecular structure of skin pigment and collect the characteristic peak signals of the pigment molecular structure; M6320 steps: Calculate the excitation signals of all resonance layers included in the skin layer, and sequentially use all resonance layer excitation signals to collect the resonance layer magnetic induction signals of all resonance layers; M6330 step: Perform steps M4100, M4200, or M4300 to obtain the pigment content in the skin.

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