Cell therapy combined with hydrogen and oxygen negative ion circulation system conditioning health management method

Abstract

The application is a cell therapy combined with hydrogen and oxygen negative ion circulation system conditioning health management method, relating to the technical field of health management and biomedical engineering, comprising: outputting hydrogen and oxygen negative ions when the dynamic oxygen uptake rate is greater than the preset upper limit mathematical threshold of safe oxygen uptake rate, and generating a cell therapy intervention time window opening trigger signal when the dynamic oxygen uptake rate is lower than the preset upper limit mathematical threshold of safe oxygen uptake rate. In the application, the double-wavelength transmission light intensity characteristic absorbance ratio parameter, the tissue oxygenation index and the cardiac output calculation data stream are synchronously acquired, the dynamic oxygen uptake rate is calculated, and the hydrogen and oxygen negative ion output and the cell therapy intervention time window are controlled according to the change, which can comprehensively reflect the circulation oxygen supply and tissue oxygen consumption state, avoid determining the intervention time according to only a single physiological parameter or a fixed time sequence, reduce the mismatch between the intervention state and the circulation state, and further improve the time sequence coordination control performance of the circulation system health management.

Description

Technical Field

[0001] This invention relates to the fields of health management and biomedical engineering technology, and in particular to a health management method that combines cell therapy with hydrogen and oxygen negative ions to regulate the circulatory system. Background Technology

[0002] With the development of physiological monitoring, microcirculation assessment, and cell health management technologies, the assessment of the circulatory system's oxygen supply and perfusion capacity based on physiological parameters such as blood oxygenation status, tissue oxygenation status, and cardiac output has been gradually applied to personalized health management scenarios. These technologies can continuously reflect the human circulatory state, providing a data foundation for intervention timing and process regulation, and are of positive significance for improving the precision of health management.

[0003] However, the actual oxygen supply status of the circulatory system is affected by multiple factors, including arterial blood oxygen levels, residual oxygen at the venous end, cardiac output, and microvascular dilation. A single blood oxygen or blood flow parameter cannot distinguish between the differences between insufficient oxygen supply and increased tissue oxygen consumption, thus making it difficult to accurately characterize dynamic oxygen uptake rate. Furthermore, the stress state of the cell suspension after entering the microcirculation changes with factors such as blood flow and vasodilation. A fixed infusion rate cannot be adjusted to accommodate changes in microvascular wall shear stress, easily leading to a mismatch between intervention timing and local circulatory status.

[0004] Current health intervention programs typically perform oxygenation regulation, cell delivery, and subsequent physiological monitoring separately, relying heavily on preset durations or fixed parameters. They lack control mechanisms to determine the intervention time window based on continuous changes in dynamic oxygen uptake rate, and also struggle to dynamically adjust the cell delivery rate in conjunction with microcirculatory status. Furthermore, maintenance status after intervention often employs fixed-cycle management, lacking continuous assessment based on the individualized intervention effect decay constant. Therefore, existing technologies have limited dynamic synergistic effects on intervention timing, delivery process, and subsequent management under different circulatory states, failing to meet the needs of individualized circulatory system conditioning and health management. Summary of the Invention

[0005] The purpose of this invention is to propose a health management method that combines cell therapy with the circulation of hydrogen and oxygen negative ions to solve the above-mentioned problems.

[0006] To achieve the above objectives, the present invention adopts the following technical solution: Cell therapy combined with hydrogen and oxygen negative ions to regulate the circulatory system and manage health includes: The data stream is calculated by obtaining the absorbance ratio parameter of dual-wavelength transmitted light intensity, tissue oxygenation index and physical characteristics of microvascular dilation, and the cardiac output is derived from the instantaneous heart rate sequence and the single ventricular stroke volume. Based on the ratio parameter of absorbance of dual-wavelength transmitted light intensity and tissue oxygenation index, the oxygen content of arterial blood and mixed venous blood is estimated, and the dynamic oxygen uptake rate is calculated by combining cardiac output with the data stream. When the dynamic oxygen uptake rate is greater than the preset safe oxygen uptake rate upper limit mathematical threshold, hydrogen and oxygen negative ions are output, and when the dynamic oxygen uptake rate is lower than the preset safe oxygen uptake rate upper limit mathematical threshold, a cell therapy intervention time window opening trigger signal is generated. After receiving the cell therapy intervention time window opening trigger signal, the dynamic value of microvascular wall shear force is estimated by calculating the data stream from cardiac output and the physical characteristic parameters of microvascular dilation. Combined with the dynamic oxygen uptake rate, the motor propulsion control pulse frequency command value is obtained and the precision injection pump is controlled. Based on the dynamic oxygen uptake rate and cardiac output data stream before and after the intervention, a joint intervention benefit index is derived. Combined with the individualized intervention effect time decay constant, the next recommended absolute physical time point for intervention is deduced.

[0007] Preferably, the process of obtaining the ratio of the characteristic absorbance of the dual-wavelength transmitted light intensity is as follows: The first center wavelength excitation source in the red light spectrum band and the second center wavelength excitation source in the near-infrared light spectrum band are driven alternately using time-division multiplexing technology. The transmitted light intensity is captured by a photodetector and the AC light intensity component and DC light intensity component are extracted by a low-noise transimpedance amplifier and an analog-to-digital conversion channel. The process of obtaining the physical characteristics of microvascular dilation is as follows: Extracted from the characteristics of photoelectric pulse waves composed of AC light intensity components and DC light intensity components; The process of obtaining the tissue oxygenation index is as follows: By using a broadband near-infrared light source emitter and multiple photodetectors arranged at equal intervals along the same straight line, the spatial differential attenuation rate of the received light intensity attenuation gradient is calculated. Combined with the specific absorption peaks of oxyhemoglobin and deoxyhemoglobin, the spectral absorption coefficient is linearly unmixed to calculate the tissue oxygenation index.

[0008] Preferably, the process of calculating the cardiac output data stream from the instantaneous heart rate sequence and the single ventricular stroke volume is as follows: A high-frequency constant current micro-alternating current is injected into the pleural cavity and the voltage drop fluctuation on the surface of the pleural cavity is captured. A cascaded digital bandpass filter is used to eliminate baseline drift, and the waveform of the pleural cavity impedance changing with time after eliminating baseline drift is extracted. First-order time differential mathematical operation is performed on the waveform of thoracic impedance change over time to generate the time-domain characteristic curve of impedance change rate, obtain the amplitude of the absolute maximum peak point and the physical time of left ventricular ejection, and multiply them with the basic resistivity constant parameter of human standard blood to obtain the single ventricular stroke volume. The instantaneous heart rate sequence is calculated by obtaining the time interval between adjacent ejection peak points, and the instantaneous heart rate sequence is multiplied by the corresponding timestamp of a single ventricular stroke to generate a cardiac output estimation data stream.

[0009] Preferably, the process of calculating the arterial blood oxygen content and the mixed venous blood oxygen content is as follows: The ratio of absorbance of dual-wavelength transmitted light intensity is mapped to the percentage of non-invasive arterial blood oxygen saturation by a second-order polynomial physical calibration equation, and the arterial blood oxygen content is obtained by combining the hemoglobin gram calibration value and physical dissolved oxygen partial pressure. By introducing a fixed vascular bed venous weight coefficient to scale the tissue oxygenation index, the percentage parameter of mixed venous blood oxygen saturation is extracted. The mixed venous blood oxygen content is then obtained by combining the hemoglobin gram calibration value and the physical dissolved oxygen partial pressure.

[0010] Preferably, the process of calculating the dynamic oxygen uptake rate is as follows: Based on the principle of physical diffusion, the oxygen delivery rate is obtained by multiplying the cardiac output data stream by the arterial blood oxygen content; the difference between the arterial blood oxygen content and the mixed venous blood oxygen content is calculated, and the difference is multiplied by the cardiac output data stream to obtain the oxygen consumption. The dynamic oxygen uptake rate is obtained by dividing the oxygen consumption by the oxygen delivery rate.

[0011] Preferably, the step of outputting hydrogen and oxygen negative ions when the dynamic oxygen uptake rate is greater than a preset safe oxygen uptake rate upper limit mathematical threshold, and generating a cell therapy intervention time window opening trigger signal when the dynamic oxygen uptake rate is lower than the preset safe oxygen uptake rate upper limit mathematical threshold, specifically includes: The system generates hydrogen by regulating the amplitude of the DC driving voltage applied to the electrodes on both sides of the electrolysis chamber, and at the same time applies a negative polarity DC pulse high voltage to the high voltage corona discharge needle array to generate a negative oxygen ion flow. The hydrogen and negative oxygen ion flow are physically mixed by a mass flow controller and output as hydrogen-oxygen negative ions. The prerequisites for generating a trigger signal to open the intervention time window for cell therapy include: Set a continuous time window threshold constant. Only when the dynamic oxygen uptake rate is continuously lower than the preset safe oxygen uptake rate upper limit mathematical threshold and this state is maintained for more than the continuous time window threshold constant on the time axis, will the cell therapy intervention time window opening trigger signal action be executed.

[0012] Preferably, the formula for calculating the DC drive voltage amplitude and the characteristic value of the drive voltage command for the negative polarity DC pulse high voltage is: ; in, This is the characteristic value of the drive voltage command; A proportional gain constant established to address the current oxygen uptake deviation; Dynamic oxygen uptake rate; A mathematical threshold for the preset safe oxygen uptake rate limit; The physical constant of the integral gain; The self-parameter of continuous virtual physical time; The theoretical constant for the physical gain of charge caused by a single negative ion in a unit volume of blood; To compensate for the physical constant of the intervention dose.

[0013] Preferably, when estimating the dynamic value of microvascular wall shear force: The apparent viscosity of microcirculatory blood was extracted and estimated, and the data stream was combined with cardiac output to calculate the characteristic value of autologous blood volume flow rate of the targeted microcirculatory bed. The volumetric flow rate of the external nutrient medium solution containing exogenous cells injected into the circulatory system by the precision injection pump was also obtained. The dynamic value of microvascular wall shear force is obtained by multiplying the estimated apparent viscosity by the sum of the characteristic value of autologous blood volumetric flow rate and volumetric flow rate, and dividing by the cubic parameter of the dynamically estimated equivalent physical radius affected by the physical characteristic parameters of microvascular dilation.

[0014] Preferably, the motor propulsion control pulse frequency command value is obtained using the following formula: ; in, This refers to the command value for the motor propulsion control pulse frequency. This is the physical constant for the pulse frequency conversion ratio; It is the critical wall shear force constant for the physical rupture of the phospholipid bilayer membrane structure; This represents the dynamic value of shear force on the microvascular wall. It is an exponential function with the natural constant as its base; The physical adjustment coefficient for oxygen uptake rate fluctuation sensitivity; Dynamic oxygen uptake rate; This is a preset mathematical threshold for the upper limit of safe oxygen uptake.

[0015] Preferably, the method of deriving a joint intervention benefit index based on the dynamic oxygen uptake rate and cardiac output data stream before and after the intervention, and combining this with the individualized intervention effect time decay constant to predict the next recommended absolute physical time point for intervention, specifically includes: The discrete numerical integration algorithm was used to perform algebraic accumulation of area micro-elements on discrete time series points reflecting the decrease in dynamic oxygen uptake rate. Combined with the improvement in large circulation hemodynamics obtained from the data stream based on cardiac output, the combined intervention benefit index was calculated. The absolute physical height, weight and age are extracted, and the basal metabolic rate constant is calculated using the basic thermodynamic empirical formula. The individualized intervention effect time decay constant is output by mapping through the linear scaling operator. Based on the preset time-domain prediction mathematical model, the absolute physical time point of the next recommended intervention is deduced using the following formula: ; in, The absolute physical time point for the next recommended intervention; The current absolute calendar physical timestamp; This represents the time decay constant of the individualized intervention effect; It is a logarithmic function with the natural constant as its base; For the joint intervention effectiveness index; This is a mathematical constant representing the lower limit of efficiency and safety.

[0016] In summary, due to the adoption of the above technical solution, the beneficial effects of the present invention are: 1. This invention calculates dynamic oxygen uptake rate by simultaneously acquiring dual-wavelength transmitted light intensity characteristic absorbance ratio parameters, tissue oxygenation index, and cardiac output data streams. Based on its changes, it controls the output of hydrogen and oxygen negative ions and the intervention time window for cell therapy. This can comprehensively reflect the state of circulatory oxygen supply and tissue oxygen consumption, and avoid determining the intervention timing based on a single physiological parameter or fixed time sequence. It reduces the mismatch between the intervention state and the circulatory state, thereby improving the time-coordinated control performance of circulatory system health management.

[0017] 2. This invention estimates the microvascular wall shear force by calculating the data stream from cardiac output and the physical characteristics of microvascular dilation, and adjusts the cell delivery rate by combining dynamic oxygen uptake rate. At the same time, it determines the subsequent management time based on the state before and after intervention and the time decay constant of individualized intervention effect. This can reduce the infusion rate mismatch caused by changes in local circulatory state, and achieve continuous management under individual differences. It avoids the inadequacy of adaptation caused by fixed pump speed and fixed cycle, thereby improving the individual adaptation performance of circulatory system health management. Attached Figure Description

[0018] Further details, features, and advantages of this application are disclosed in the following description of exemplary embodiments in conjunction with the accompanying drawings, in which: Figure 1 This is a flowchart of the method of the present invention. Detailed Implementation

[0019] Several embodiments of this application will now be described in more detail with reference to the accompanying drawings to enable those skilled in the art to implement this application. This application may be embodied in many different forms and for various purposes and should not be limited to the embodiments set forth herein. These embodiments are provided to make this application thorough and complete, and to fully convey the scope of this application to those skilled in the art. The embodiments described do not limit this application.

[0020] Unless otherwise defined, all terms used herein (including technical and scientific terms) shall have the same meaning as commonly understood by one of ordinary skill in the art to which this application pertains. It will be further understood that terms such as those defined in commonly used dictionaries shall be interpreted as having a meaning consistent with their meaning in the relevant field and / or the context of this specification, and shall not be interpreted in an idealized or overly formal sense unless expressly defined herein.

[0021] Example 1 Its specific implementation method is combined with the appendix Figure 1 Please provide a detailed explanation.

[0022] Appendix Figure 1 The flowchart of the health management method for regulating the circulatory system by combining cell therapy with hydrogen and oxygen negative ions provided in the embodiments of the present invention shows the complete steps from the collection of multi-source data on circulatory physiology to the mathematical evaluation of the post-intervention effect.

[0023] In this embodiment, it includes: Step 1, Circulatory physiological multi-source data acquisition: Obtain the dual-wavelength transmitted light intensity characteristic absorbance ratio parameter, tissue oxygenation index and microvascular dilation physical characteristic parameters, and calculate cardiac output from instantaneous heart rate sequence and single ventricular stroke volume to estimate data stream; This step involves constructing a non-invasive, time-series physiological information acquisition architecture to continuously acquire the human body's non-invasive arterial blood oxygen saturation estimation percentage, mixed venous blood oxygenation status characteristics, and basic cardiac output parameters from the underlying physics and electronics.

[0024] These parameters are indispensable independent input parameters for the subsequent establishment of the oxygen uptake rate calculation equation.

[0025] When taking in these parameters, the system needs to establish a front-end sensing link with a high common-mode rejection ratio to eliminate power frequency interference and electromyographic noise caused by the subject's slight limb movements, thereby ensuring that the self-parameters used for subsequent mathematical equation derivation have strict physical authenticity.

[0026] The system's time-series physiological information acquisition architecture not only relies on independent hardware channels, but also incorporates multiple physical isolation mechanisms at the underlying level to prevent electromagnetic crosstalk between sensing signals of different frequency bands.

[0027] The system executes an arterial blood oxygenation signal acquisition process based on a multi-wavelength photoplethysmography pulse wave sensing architecture, deploying photoelectric probe components in areas rich in peripheral microvessels (such as fingertips or earlobes) of the subject.

[0028] The component contains two narrow-band light-emitting diodes that emit light at a specific physical geometric angle as the excitation light source.

[0029] These two types of LEDs are each equipped with independent programmable constant current drive circuits to ensure that the emission power of the beam maintains an absolutely stable physical output intensity when facing human tissue of different thicknesses.

[0030] The central physical wavelength of the first excitation light source is precisely set to 660 nanometers, which is in the red light spectrum band; The central physical wavelength of the second excitation light source is precisely set to 940 nanometers, which is in the near-infrared spectral band.

[0031] The physical basis for choosing these two wavelengths is that there is a significant physical difference in the photon absorption cross-section between oxyhemoglobin containing oxygen molecules and deoxyhemoglobin without oxygen molecules in these two frequency bands.

[0032] Specifically, at a wavelength of 660 nm, the light absorption coefficient of deoxyhemoglobin is much greater than that of oxyhemoglobin; however, at a wavelength of 940 nm, the light absorption coefficient of oxyhemoglobin is reversed and becomes greater than that of deoxyhemoglobin.

[0033] A high-quantum-efficiency photodiode receiver is arranged on the opposite side of the probe to collect the residual photon energy that has not been absorbed after penetrating human finger or earlobe tissue.

[0034] When the heart contracts and relaxes rhythmically, the physical diameter of the peripheral arteries and the volume of blood within them undergo periodic pulsatile expansion and contraction. This change in blood volume causes a dynamic change in the optical path length, resulting in the transmitted light intensity captured by the receiver exhibiting a mixed waveform that includes a constant DC absorption baseline (composed of static absorption from skin pigment, bone, muscle, and venous blood) and an AC pulsatile absorption component (composed purely of absorption from the increased blood volume caused by arterial contraction and relaxation).

[0035] The photodetector converts the captured photon energy into a weak photocurrent signal, which is then passed to a pre-amplifier network of low-noise transimpedance amplifiers for a linear physical current-to-voltage conversion. The converted voltage signal passes through an anti-aliasing low-pass filter with a cutoff frequency set at tens of hertz to suppress high-frequency spatial electromagnetic noise. It then enters a high-precision 24-bit successive approximation or Σ-Δ analog-to-digital converter channel, converting the continuous analog voltage into a discrete digital time-series signal.

[0036] During this process, the system uses time-division multiplexing technology to alternately illuminate red light and near-infrared light sources within a millisecond-level time window and record the corresponding dark current baseline to eliminate DC offset interference caused by ambient background light.

[0037] The central processing unit uses a sliding analysis window with a fixed time width and employs morphological extreme value detection algorithms and zero-crossing point recognition technology to decompose the digital waveform extracted at each wavelength into DC light intensity components representing the absorption of static tissues such as venous blood, bones, and muscles, and AC light intensity components representing the absorption of arterial pulsating blood.

[0038] Based on the modified Lambert-Beer law of light absorption, the system calculates a light absorption modulation ratio parameter that reflects the state of arterial blood oxygen saturation. The calculation formula is as follows: ; in, parameter Defined as the characteristic absorbance ratio of the two wavelengths of transmitted light intensity, this parameter has a deterministic mapping relationship with arterial blood oxygen saturation with a negative correlation. parameter Defined as the amplitude of the AC component of the transmitted light signal resolved at the first center wavelength (660 nm); parameter Defined as the amplitude of the DC component of the transmitted light signal resolved at the first center wavelength; parameter Defined as the amplitude of the AC component of the transmitted light signal resolved at the second center wavelength (940 nm); parameter It is defined as the amplitude of the DC component of the transmitted light signal resolved at the second center wavelength.

[0039] The physical characteristic parameter of microvascular dilation is defined as the ratio of the arterial pulsatile absorption component to the static absorption component in the photoelectric pulse wave, and the calculation formula is: ; in, parameter Defined at time node The physical characteristic parameter of microvascular dilation is measured, and this ratio increases with the increase of the degree of peripheral microvascular dilation. The system... Output after performing a moving average process.

[0040] By continuously calculating this ratio parameter, the system constructs an uninterrupted data stream of arterial blood flow oxygenation characteristics, laying the foundation for the calculation of oxygen delivery volume using basic parameters at the arterial end.

[0041] The system executes in parallel a process for approximating the oxygenation of mixed venous blood in deep tissues based on continuous spatial resolution near-infrared spectroscopy. To avoid the traditional invasive central venous catheterization oxygenation procedure (which carries an extremely high risk of infection and is unsuitable for routine health management), this approach uses an optical spatial gradient analysis physical model to calculate the comprehensive oxygenation index of local tissues, which serves as an alternative measurement of mixed venous blood oxygenation.

[0042] A special diffuse reflection optical probe array is attached to a flat area of ​​the subject's forearm or frontal lobe. The probe array consists of a broadband continuously emitting near-infrared light source and three highly sensitive photodetectors (avalanche photodiodes) arranged at equal physical intervals along the same straight line.

[0043] After the near-infrared beam emitted by the light source enters human tissue, it undergoes a complex multi-dimensional physical scattering and absorption process, forming a photon propagation path similar to a "banana".

[0044] Because near-infrared light has a relatively small absorption coefficient and a very large scattering coefficient in biological tissues (which conforms to the optical physical characteristics of high scattering and weak absorption), photons can penetrate the skin surface and reach the microcirculation bed below the dermis (the blood in the microcirculation bed is mainly composed of venous blood and some capillary blood, with venous components occupying an absolute dominant position, and the volume ratio usually exceeding 70%).

[0045] Three photodetectors located at different physical distances collect light intensity signals diffusely reflected back from tissues at different depths. The system mathematically calculates the light intensity attenuation gradient received by the detectors at different distances based on the analytical solution of the steady-state radiative transport and diffusion equation for photons in strongly scattering media.

[0046] Since superficial tissues (such as epidermal pigment and subcutaneous fat) have a nearly uniform and constant background characteristic in their effect on the optical path attenuation of all distance detectors, the system directly cancels the background interference of superficial static tissues from a mathematical perspective by calculating the differential attenuation rate of spatial distance, thus separately isolating the spectral absorption coefficient of hemoglobin in the deep microcirculation bed. .

[0047] Furthermore, based on the steady-state radiative transport and diffusion equation of photons in a strongly scattering medium, the system calculates the spatial differential attenuation rate from the received light intensity of three photodetectors arranged at equal intervals along the same straight line. The spectral absorption coefficient is ; Among them, parameters Defined as the tissue-reduced scattering coefficient, taken as an empirical constant for tissue optics; The system then established a system of linear equations at two characteristic wavelengths: red light and near-infrared light. The concentration of oxyhemoglobin was obtained. With reduced hemoglobin concentration ; in, , Defined as the molar absorptivity of oxyhemoglobin and deoxyhemoglobin at the emission wavelength parameter λ, taking the empirical constant of hemoglobin spectral absorption; Tissue oxygenation index is .

[0048] This sequence serves as the physical basis for calculating mixed venous blood oxygenation status and is continuously input into the next level of the processing buffer.

[0049] The system synchronously initiates the cardiac output baseline parameter acquisition process based on high-frequency micro-electrophysiological impedance excitation. The dynamic change of cardiac output is the decisive physical parameter for measuring oxygen delivery efficiency. Blood oxygen saturation alone, without blood flow parameters, cannot truly reflect the carrying capacity of the circulatory system.

[0050] This method relies on the physical phenomenon of changes in thoracic conductivity to inversely calculate ventricular pumping performance. Four-electrode arrays are attached to both sides of the subject's neck root and both sides of the chest at the xiphoid process level. The electrode arrays consist of outer current-excitation electrode pairs and inner voltage-sensing electrode pairs. The excitation control circuit injects a high-frequency constant-current micro-alternating current into the subject's thoracic cavity via the outer electrode pairs. The frequency is set between 50 kHz and 100 kHz, and the effective current amplitude is limited to between 2 mA and 4 mA.

[0051] The high-frequency microcurrent in this frequency band has extremely high tissue penetration capability and is completely below the depolarization excitation threshold of human nerves and muscles, belonging to the purely physical level of safe induced current.

[0052] Because the human thoracic cavity contains lung chambers, bones, muscles, and large blood vessels, which are media with different conductivity, the thoracic cavity can be regarded as a complex cylindrical conductive model composed of multiple impedances connected in parallel. Among them, the conductivity of blood in the aorta is significantly higher than that of other surrounding tissues (blood is rich in free electrolyte ions).

[0053] When the left ventricle contracts and ejects blood into the aorta, the volume of the aorta expands rapidly. Red blood cells align axially under the shear force of the blood flow, and the proportion of the space containing the highly conductive medium (blood) in the thoracic cavity increases instantaneously, resulting in a pulsatile physical decrease in the overall electrical impedance of the thoracic cavity. Conversely, when the ventricle relaxes and blood flows out of the thoracic cavity, the electrical impedance increases.

[0054] The voltage sensing electrode located on the inner side continuously captures the characteristics of minute voltage drop fluctuations on the surface of the thoracic cavity.

[0055] Since a constant alternating current is injected, according to Ohm's law of physics, the voltage drop fluctuations are directly proportional to the sum of the basic static impedance of the thoracic cavity and the superimposed tiny alternating pulsating impedance.

[0056] The system's internal synchronous demodulation hardware module first strips the high-frequency carrier signal, restoring the original impedance change signal containing low-frequency drift in respiratory rhythm and high-frequency fluctuations in cardiac rhythm. Through a cascaded digital bandpass filter (with the passband frequency range strictly set between 0.5 Hz and 10 Hz, employing a finite-length unit impulse response filter structure with linear phase characteristics), the system separates and eliminates the impedance baseline drift caused by the mechanical movement of the chest cavity during breathing (which generates a large low-frequency component), ultimately extracting the pure waveform envelope of the cardiac cycle's thoracic cavity impedance changing over time.

[0057] For the extracted pure impedance waveform, the system performs a first-order time differential mathematical operation on it to generate a time-domain characteristic curve of the impedance change rate (i.e., Waveform).

[0058] Using the characteristic markers on the differential characteristic curve (such as point B representing the start of ejection, point C representing the maximum ejection velocity, and point X representing the closure of the aortic valve) and the anatomical measurement constants of the body surface, the system calculates the basic physical parameters of the single ventricular stroke volume based on the Kubicek cylinder impedance model or the modified Sramek-Bernstein geometric model.

[0059] The formula is expressed as follows: ; in, parameter Defined as the estimated volume of blood ejected from the aorta during a single heartbeat, calculated using a bioimpedance physical model; parameter Defined as the basic resistivity constant parameter of standard human blood, this value is calibrated based on the subject's basic physiological information; parameter Defined as the vertical surface anatomical physical distance between two sets of internal voltage sensing electrode pairs in the thoracic cavity; parameter Defined as the baseline static impedance value of the thoracic cavity obtained after the system has undergone long-term smoothing and averaging. parameter Defined as the amplitude of the absolute maximum peak point (usually corresponding to point C of the differential waveform) in the first time derivative waveform of the rate of change of thoracic impedance during a single ventricular systole, representing the physical characteristics of the maximum ventricular ejection acceleration; parameter Defined as the physical duration of left ventricular ejection, its value is obtained by measuring the time interval between the maximum positive peak in the differential waveform of impedance change and the characteristic notch (X point) representing the aortic valve closure feature.

[0060] By continuously calculating the estimated cardiac output volume and combining it with the real-time heart rate frequency parameters extracted from the pulse waveform, the system can calculate a continuous data stream of estimated cardiac output in real time.

[0061] To ensure the temporal logic of the three parallel data acquisition links (photoelectric pulse blood oxygenation link, spatial spectrum venous substitution link, and micro-frequency impedance blood flow link) in subsequent calculations, the system deploys a high-frequency central quartz clock source in the underlying hardware architecture.

[0062] Due to objective hardware differences in the analog-to-digital conversion sampling frequencies of the three physical sensors (for example, the sampling rate of the impedance channel is usually much higher than that of the photoelectric channel), the central processing unit forcibly adds a global timestamp with nanosecond-level precision when receiving the underlying data packets of each channel. To address the problem of discrete time point misalignment caused by sampling rate mismatch, the system does not rely on any statistical probability model, but instead adopts a deterministic Lagrange polynomial mathematical interpolation resampling algorithm to strictly align and map the discrete data points of all feature parameters onto the same high-resolution base time axis.

[0063] All arterial absorbance characteristic parameters, deep tissue oxygenation characteristic parameters, and cardiac output physical characteristic parameters, after alignment, filtering, and preliminary formula transformation, are encapsulated into periodic time-series payloads with a unified data structure and continuously delivered to the core logic operation layer.

[0064] Step 2, Dynamic calculation of oxygen uptake rate: Based on the ratio parameter of absorbance of dual-wavelength transmitted light intensity and tissue oxygenation index, the oxygen content of arterial blood and mixed venous blood is calculated, and the dynamic oxygen uptake rate is calculated by combining the data stream of cardiac output. Based on the continuous, aligned, and high temporal resolution low-level physiological feature signal sequence obtained in Step 1, this step constructs a mathematical deduction framework for dynamic oxygen uptake rate under non-invasive conditions through physicochemical constant mapping and classical physiological dynamic equations.

[0065] In the conventional process of exogenous cell infusion, if the local tissue of the host is in a state of high oxygen consumption (i.e., the oxygen uptake rate is too high), it means that the oxygen supply of the microcirculation in the target area is less than the oxygen consumption. The infused therapeutic cells will be forced to engage in a brutal "oxygen consumption competition" with the host's original tissue. This physical resource deprivation at the microenvironment level will cause the infused cells to undergo large-scale apoptosis due to acute hypoxia and inability to synthesize enough adenosine triphosphate (ATP).

[0066] The system retrieves the dual-wavelength transmitted light intensity characteristic absorbance ratio parameter sequence generated in step one. This is converted into a continuous arterial oxygen saturation estimate.

[0067] Based on the nonlinear physical diffraction characteristics of the Lambert-Beer law and the dynamic multiple scattering effect of red blood cells in blood vessels as the flow rate changes, the system does not use simple linear scaling, but instead uses a pre-set empirical second-order polynomial physical calibration equation for conversion.

[0068] The second-order polynomial physical calibration equation is in the form of: ; in, parameter , , Defined as a calibration coefficient, it is obtained by simultaneously collecting the ratio of dual-wavelength transmitted light intensity characteristic absorbance in a healthy subject population and measuring arterial blood oxygen saturation using an arterial blood gas analyzer, and then performing least-squares fitting calibration. For example... Take 110, Take -30, Take 5.

[0069] The equation fits the comprehensive attenuation characteristics of photon scattering and absorption in whole blood medium using mathematical constants, and calculates the non-invasive arterial blood oxygen saturation estimation sequence.

[0070] The system retrieves the tissue oxygenation index time series output by spatially resolved near-infrared spectroscopy. Since the microcirculation bed contains three main blood flow convergence layers: arterioles, capillaries, and venules, in order to achieve accurate assessment of the residual oxygen status at the venous return end, the system sets a fixed venous weight coefficient for the vascular bed based on the constant physical proportion of microcirculation blood volume distribution in human anatomy (usually, venule blood volume accounts for the vast majority of the total microcirculation blood volume, about 75% to 80%).

[0071] The system is based on the formula Calculate the inferred sequence of mixed venous oxygen saturation; in, parameter Defined as the fixed vein weighting coefficient for the vascular bed, fixed at 0.75; parameter Defined as the compensation for the local tissue physical light absorption constant, it is a calibration constant, calibrated by comparison with the measured values ​​of venous blood gas during the same period, and its value ranges from -0.05 to 0.05.

[0072] The system introduces an absolute physical calculation model for oxygen content; Oxygen in the blood consists of two physical states: One is bound oxygen that undergoes a reversible chemical binding with hemoglobin molecules inside red blood cells; Secondly, according to Henry's law of physics (the solubility of a gas in a liquid is proportional to the partial pressure on the surface of the liquid), dissolved oxygen directly dissolves in the plasma.

[0073] Although dissolved oxygen accounts for a very small proportion under normal pressure, its physical gain becomes a decisive factor when high pressure or specific electric field physical interventions (such as subsequent hydrogen and oxygen negative ion interventions) are introduced, and therefore cannot be ignored in the extrapolation model.

[0074] The system retrieves the baseline hemoglobin concentration calibration value of the subject from external input and combines it with the obtained arterial and venous blood oxygen saturation sequences to establish dynamic equations for arterial blood oxygen content and mixed venous blood oxygen content, respectively.

[0075] The formula for its arterial blood oxygen content is as follows: ; in, parameter Defined at time node The total volume of oxygen contained in every 100 milliliters of arterial blood; parameter Defined as the Hefner constant, its value is constant at 1.34, representing the number of milliliters of oxygen that one gram of pure hemoglobin can chemically bind to in a fully saturated state; parameter Defined as the calibrated value of hemoglobin grams per 100 milliliters of blood in the subject, it is used as the input of the basic setting parameter; parameter Defined as the system at time node The estimated percentage of non-invasive arterial oxygen saturation is obtained through second-order polynomial calibration calculation; parameter Defined as the physical solubility constant of oxygen in blood plasma at normal human body temperature (usually set at 37 degrees Celsius), its value is fixed at 0.0031; parameter Defined as a mathematical estimate of the partial pressure of oxygen in arterial blood, this value is derived from the standard mathematical inverse function of the oxygen dissociation curve (based on the acid-base compensation and temperature physical compensation constants of the Bohr effect, for example, derived using the inverse Severinghaus empirical equation). It was deduced.

[0076] Similarly, the system uses the same mathematical logic and mixed venous blood oxygen saturation prediction sequence to construct an independent continuous calculation equation for mixed venous blood oxygen content; The formula is as follows: ; in, parameter Defined at time node The total volume of oxygen contained in 100 milliliters of mixed venous blood; parameter Defined as the system at time node The mixed venous blood oxygen saturation percentage parameter is calculated based on spatially resolved near-infrared spectroscopy and venous weighting coefficient. parameter Defined as a mathematical estimate of the partial pressure of oxygen in mixed venous blood, this value is also derived from the standard mathematical inverse function of the oxygen dissociation curve. It can be deduced; constant and The physical definition and numerical value are consistent with the formula for arterial blood oxygen content.

[0077] Calculate the continuous sequence of mixed venous blood oxygen content representing the residual oxygen level at the venous return end. .

[0078] These two sequences represent the source potential energy for oxygen input into the tissue and the residual exhaust potential energy after tissue consumption, respectively. The physical difference between them is the absolute scale of the actual oxygen consumption of the microenvironment tissue.

[0079] After obtaining the absolute values ​​of arterial and venous blood oxygen content, the system initiates the calculation of key oxygen dynamic flow parameters in parallel.

[0080] The system retrieves the pure impedance differential waveform extracted in step one, calculates the time interval between the ejection peak points (maximum peak points of impedance derivative) of two adjacent cardiac cycles, takes its reciprocal and multiplies it by the time conversion constant (e.g., multiply by 60 to convert to heart rate per minute), and calculates a high-precision instantaneous heart rate sequence.

[0081] The estimated volume of blood ejected from the aorta during a single heartbeat, obtained in step one ( The instantaneous heart rate sequence is multiplied by the corresponding timestamp to generate a continuous cardiac output estimation data stream (the total volume of blood pumped into the aorta by the heart per unit time).

[0082] At this point, the system possesses all the underlying physical and biochemical mapping parameters for calculating the whole-body circulatory oxygen uptake rate. Based on the macroscopic extension of Fick's first physical principle of diffusion, the system constructs a continuous oxygen delivery system. Equation and oxygen consumption equation.

[0083] Oxygen delivery is defined as the product of the estimated cardiac output data stream and the arterial blood oxygen content. It represents the total amount of oxygen physically delivered to peripheral tissues by the circulatory system per unit time. This parameter is the basis for determining whether exogenous cells can obtain the oxygen resources necessary for survival in the initial stage of injection. Oxygen consumption is defined as the product of the estimated cardiac output data stream and the difference between arterial and venous blood oxygen content (i.e., arterial blood delivery minus venous blood residue). It represents the actual amount of oxygen consumed by tissues per unit time and involved in the physical and biochemical reactions of intracellular mitochondrial aerobic metabolism.

[0084] The system calculates the dynamic oxygen uptake characteristic curve, which has core control significance, and its formula is as follows: ; in, parameter Defined at time node The dynamic oxygen uptake rate at any given moment, which is presented as a dimensionless decimal or percentage, directly reflects the degree of oxygen hunger of the host tissues in the current circulatory system. parameter Defined as a time node The overall oxygen consumption at the time; parameter Defined as a time node The overall oxygen delivery rate at the time of the measurement; parameter With parameters These represent the derived arterial blood oxygen content and mixed venous blood oxygen content, respectively.

[0085] When that A significant increase in values ​​indicates that the host tissue's basal metabolism has extracted excessive amounts of oxygen from the blood, and the microcirculation bed is in a highly hypoxic and oxygen-consuming physicochemical environment. If cell-cell injection is performed blindly at this time, the cells will undergo large-scale apoptosis due to hypoxia.

[0086] The system will put the dimensionless characteristic curve of this continuous calculation output into the internal safe and isolated high-speed cache as the sole mathematical basis for determining the danger level of "oxygen consumption competition". It will also directly use it as a signal input source to transmit to the next physical intervention control module for threshold comparison and linkage control with external hardware devices (such as hydrogen-oxygen negative ion generators).

[0087] Step 3, Ion Intervention Pressure Drop Assessment and Control: When the dynamic oxygen uptake rate is greater than the preset safe oxygen uptake rate upper limit mathematical threshold, hydrogen and oxygen negative ions are output, and when the dynamic oxygen uptake rate is lower than the preset safe oxygen uptake rate upper limit mathematical threshold, a cell therapy intervention time window opening trigger signal is generated. Based on the dynamic oxygen uptake rate curve continuously output in step two, this step establishes a physical gas and electric field intervention control system driven by pure mathematical logic.

[0088] By precisely introducing a specific mixture of hydrogen molecules and oxygen ions carrying a high voltage and negative charge (collectively referred to as hydrogen-oxygen anion) into the respiratory tract, the oxygen delivery to the basal layer of the circulation is artificially intervened and significantly increased by utilizing their physical diffusion effect on the alveolar air-blood barrier and their physical modification effect on the erythrocyte membrane potential. This mathematically forces the abnormally high oxygen uptake rate to "drop" until it falls below the oxygen-consuming competition safety line suitable for the survival of exogenous cells.

[0089] This purely physical intervention not only avoids the burden on the liver and kidneys caused by the metabolism of traditional chemical drugs, but also achieves millisecond-level response and cessation.

[0090] The system first initializes a series of physical intervention comparison thresholds in its internal logic registers. These include: a preset safe oxygen uptake rate upper limit mathematical threshold to prevent oxygen consumption competition (the preset safe oxygen uptake rate upper limit mathematical threshold is the sum of the subject's resting baseline oxygen uptake rate and a preset upward margin, with the preset upward margin being greater than zero; for example, when the subject's resting baseline oxygen uptake rate is 0.22 and the preset upward margin is 0.08, the preset safe oxygen uptake rate upper limit mathematical threshold is 0.30), and a continuous time window threshold constant for determining system stability.

[0091] The system's core processing unit retrieves real-time updated dynamic oxygen uptake rate data points and performs high-speed continuous difference calculations with preset safety upper limit mathematical thresholds.

[0092] When the calculated dynamic oxygen uptake rate is high and exceeds the safety upper limit threshold, the system immediately generates a hardware interrupt signal and initiates a hardware-level physical intervention pressure drop control sequence.

[0093] The system sends a primary physics start-up simulation command to the externally connected hydrogen-oxygen negative ion generating hardware via its internal digital-to-analog conversion module. This hardware has a complex dual physics generation architecture, comprising a pure water electrolysis chamber and a high-voltage corona discharge needle array.

[0094] In the electrolysis chamber, the system controls the amplitude of the DC driving voltage applied to the titanium-based platinum-coated electrodes on both sides of the proton exchange membrane via commands. The intensity of the DC current in the electrolysis circuit changes monotonically with the amplitude of the DC driving voltage. According to Faraday's law of electrolysis, the molar flow rate of hydrogen molecules is proportional to the intensity of the DC current. The system regulates the molar flow rate of hydrogen molecules by adjusting the amplitude of the DC driving voltage. The effective electrolysis area of ​​the electrolysis electrodes is set to 20 to 50 square centimeters, and the operating range of the DC current intensity is 0.5 to 2 amperes. At the same time, the system applies a negative polarity DC pulse high voltage of five to eight kilovolts to the independently packaged high-voltage corona discharge needle bundle (using tungsten-gold alloy needle tips with extremely small curvature radius).

[0095] Free electrons in the air collide with oxygen molecules under the strong acceleration of the electric field gradient, causing them to undergo an electron capture effect under the action of the strong electric field force, forming a physical negative oxygen ion flow with a specific mobility.

[0096] The airflow residence time in the corona discharge area is set to a preset residence time. A manganese dioxide catalytic decomposition filter is installed downstream of the discharge needle bundle. The output gas is monitored online by an ozone concentration sensor. The ozone volume fraction is controlled to be less than 0.05 ppm and the nitrogen oxide volume fraction is controlled to be less than 0.1 ppm. When the ozone volume fraction is not less than 0.05 ppm, the system cuts off the negative polarity DC pulse high voltage and stops outputting hydrogen and oxygen negative ions. The system uses a mass flow controller equipped with a high-precision microelectromechanical system (MEMS) sensor to physically mix high-purity hydrogen gas with a high-concentration negative oxygen ion stream according to a calculated ratio. The ratio calculation rules are as follows: the hydrogen gas fraction is set to 1% to 3%, which is less than the 4% lower limit for hydrogen combustion and explosion; the negative oxygen ion concentration is set to... to Each cubic centimeter; the total output flow rate is set to 2 to 6 liters per minute; the hydrogen molar flow rate and the driving voltage command characteristic value are linearly mapped according to a preset proportional coefficient, and delivered to the subject's breathing mask through a non-conductive anti-static gas delivery pipeline.

[0097] To reduce the oxygen uptake rate, the system constructed a continuous control physical model that integrates feedforward and feedback.

[0098] After hydrogen and oxygen negative ions enter the alveolar capillary network through the respiratory system and then enter the systemic bloodstream, they produce two core physical and biochemical corrective effects: First, hydrogen molecules have extremely small molecular weights and extremely high tissue penetration. Their strong reducing properties allow them to directly cross the blood-brain barrier and cell membranes, consuming excess reactive oxygen species in the targeted microcirculation. This chemical neutralization reaction is equivalent to a dynamic buffering effect, causing a slight change in the concentration of free hydrogen ions in the blood microenvironment. According to the theoretical physical mechanism of the Bohr effect, subtle changes in blood pH can alter the stability of salt bonds within hemoglobin molecules, causing an allosteric effect in the conformation of hemoglobin. This, in turn, leads to a nonlinear shift in the oxygen dissociation curve (a rightward shift increases oxygen release capacity), directly improving the physical efficiency of oxygen diffusion from hemoglobin to tissues. Second, the negative oxygen ions in the inhaled airflow undergo charge neutralization at the air-fluid interface between the respiratory mucosa and the alveoli, and do not enter the blood circulation as free radicals; the partial pressure of oxygen in the mixed gas is higher than that of oxygen in the air. According to Henry's Law, the increase in the partial pressure of oxygen in the alveolar gas increases the physical dissolved oxygen content in the blood plasma. Hydrogen and negative oxygen ions in the mixed gas do not spontaneously react at room temperature and pressure. The two are transported to the inlet of the breathing mask through independent gas delivery pipelines and mixed. In this application, hydrogen-oxygen negative ions refer to the mixed gas formed by hydrogen and negative oxygen ions. On the other hand, negatively charged ion currents adhere to the surface of red blood cells, increasing the zeta potential of the red blood cell surface. According to the electrostatic repulsion principle of colloid physics, the mutual repulsion between red blood cells is significantly enhanced, thereby greatly reducing the abnormal aggregation index of red blood cells. This leads to a significant physical decrease in whole blood viscosity under non-Newtonian fluid conditions, which in turn physically accelerates the laminar flow rate of blood in the microcirculation.

[0099] The system transforms this complex biophysical intervention effect into a mathematical compensation calculation formula (based on the proportional-integral dual-modal control law equation) for real-time calculation of the control voltage parameters required by the intervention device: ; in, parameter Defined as the system at time node The characteristic value of the drive voltage command output to the high voltage control motherboard of the hydrogen-oxygen negative ion generator is recorded. parameter Defined as a proportional gain constant set for the current oxygen uptake rate deviation, it is purely used to amplify the error value at the current moment through mathematical multiplication without delay in order to speed up the system response; parameter Defined as the calculated amount of actual oxygen uptake rate of the current circulation system continuously input in step two; parameter Defined as a pre-set mathematical threshold constant for the upper limit of safe oxygen uptake rate to prevent competition for oxygen consumption by cells; parameter Defined as the physical constant of integral gain for historical oxygen uptake rate deviation, it is used to eliminate the static calculation residual error caused by pure proportional control by accumulating historical errors; parameter Defined as a continuous virtual physical time parameter during the time integration process, its value ranges continuously from the zero moment of intervention initiation to the current moment. ; parameter Defined as from the moment the intervention was initiated to the present. During the specified period, the cumulative mathematical time integral of the portion of the actual oxygen uptake rate that exceeds the safety threshold represents the total time-depth area of ​​the system's exposure to hypoxia risk. parameter Defined as the theoretical constant of the physical gain of charge caused by a single negative ion in a unit volume of blood; parameter Defined as the physical constant of intervention dose compensation calculated based on the subject's body surface area and estimated total blood volume.

[0100] Through continuous multi-threaded calculations of the above difference equations, the system continuously and dynamically adjusts the driving parameters output to the hydrogen-oxygen negative ion generator.

[0101] When the dynamic oxygen uptake rate is less than the preset safe oxygen uptake rate upper limit mathematical threshold, the system resets the mathematical time integral accumulation to zero; when the drive voltage command characteristic value reaches the preset voltage upper limit, the integral term stops accumulating until the dynamic oxygen uptake rate is greater than the preset safe oxygen uptake rate upper limit mathematical threshold again; based on parameters With parameters The bias term is used to set the baseline intervention intensity based on the subject's body surface area and estimated total blood volume, so that the output at the intervention initiation time matches the individual blood volume of the subject.

[0102] As high concentrations of hydrogen and oxygen negative ions diffuse into the arterial blood pumped out by the ventricle via the respiratory tract, the dissolved oxygen content in the blood is forcibly increased. Furthermore, the improved rheology due to the increased erythrocyte zeta potential leads to a slight increase in microscopic blood flow. The combined effect of these two physical mechanisms results in increased oxygen delivery. The denominator undergoes a physical expansion.

[0103] At the same time, the neutralization of free radicals reduces the amount of ineffective metabolic oxygen consumption caused by inflammatory responses, etc. The number of molecules decreases.

[0104] The simultaneous change in the physical parameters of decreasing numerator and increasing denominator jointly drives the dynamic oxygen uptake curve received by the system feedback to show a clear downward trend in pressure drop.

[0105] The system continuously performs millisecond-level clock tick comparison and verification, constructing a purely data-driven dynamic timeline monitoring link.

[0106] The system sets up a strict conditional state machine in this link: only when the real-time calculated dynamic oxygen uptake rate value is available... continuously below the set safety upper limit mathematical threshold Furthermore, only when this target state is maintained continuously on the time axis for a specific time constant (which is set to be greater than the physical time required for blood to complete at least one full body circulation and pulmonary circulation, usually calculated based on the subject's heart rate, for example, set to 180 seconds), does the system logically determine that the risk of "oxygen consumption competition" in the microcirculation bed has been effectively suppressed to a safe range.

[0107] If a transient spike occurs in the oxygen uptake rate during the time constant countdown, the state machine will immediately reset and restart the countdown, thus completely avoiding premature intervention and misjudgment caused by transient fluctuations in physiological parameters.

[0108] Once these stringent time and threshold conditions are met, it indicates that the risk of acute apoptosis caused by oxygen consumption competition has been systematically eliminated. The system's core will immediately generate a "cell therapy intervention time window opening" level trigger signal containing a specific digital encrypted signature, and send this physical level signal directly to the external medical pump terminal responsible for cell infusion via an isolated industrial-grade communication bus.

[0109] Step 4, Cell delivery rate coordinated control: After receiving the cell therapy intervention time window opening trigger signal, the dynamic value of microvascular wall shear force is estimated by calculating the data stream from cardiac output and the physical characteristic parameters of microvascular dilation, and combined with the dynamic oxygen uptake rate to obtain the motor propulsion control pulse frequency command value and control the precision injection pump.

[0110] The core objective of this step is to successfully capture the dynamic oxygen uptake rate pressure drop state brought about by the physical intervention of hydrogen and oxygen negative ions in step three, and after receiving the "cell therapy intervention time window opening" trigger signal, establish a dual safety constraint infusion mechanism that is strictly limited by microcirculation fluid dynamic parameters and real-time oxygen dynamic parameters.

[0111] Because the phospholipid bilayer structure of exogenous therapeutic cells (such as mesenchymal stem cells or specific immune cells) is fragile when they leave the in vitro culture chamber and enter the complex circulatory system of the human body.

[0112] They not only require the low-oxygen-consumption, high-oxygen-carrying microenvironment created in step three above, but also absolutely need to avoid the high mechanical friction caused by abnormal blood rheology inside the microvessels. This wall shear force, dominated by fluid viscous shear stress, will directly produce mechanical tearing if it exceeds the tensile yield limit of the cell membrane surface, leading to the leakage of cell contents and cell inactivation.

[0113] Therefore, the system needs to use a pure mathematical calculation module, combined with blood fluid dynamics equations, to regulate the physical propulsion rate of exogenous cells entering the blood vessels in real time.

[0114] When the system's main control logic unit receives a trigger signal, it first sends a hardware handshake and initialization calibration command to the externally connected medical precision infusion pump via an isolated serial data communication bus (e.g., using RS-485 or CAN physical bus protocol). The infusion pump is internally equipped with a high-resolution stepper motor with an extremely small step angle and a precision-machined ball screw helical push rod transmission mechanism.

[0115] The stepper motor driver uses microstepping technology, which can subdivide each physical step angle into hundreds of microsteps, enabling the push rod to perform smooth liquid physical propulsion with extreme physical precision of microliters per minute (or even nanoliters per minute).

[0116] Before initiating physical propulsion, the system concurrently activates a real-time mathematical estimation model of the shear force on the walls of the microvascular network. Blood is not a homogeneous ideal liquid, but a non-Newtonian fluid containing a large number of suspended particles (red blood cells, white blood cells, platelets, etc.).

[0117] In the microcirculation, the apparent viscosity of blood changes significantly as the diameter of blood vessels narrows sharply. At the same time, the axial concentration of red blood cells in the central region of microvessels leads to changes in the thickness of the plasma layer near the vessel wall.

[0118] The system retrieves the cardiac output estimation data stream obtained from high-frequency micro-electrophysiological impedance in step one, and combines it with the microvascular dilation physical characteristic parameters extracted from photoelectric pulse wave features. Based on the Hagen-Poiseuille physical fluid law, parameterization processing is performed at the microcirculation scale. Based on the extended application of the Hagen-Poiseuille physical fluid law, for the laminar flow state of whole blood with non-Newtonian fluid characteristics in micro-cylindrical channels, the system constructs the following real-time estimation formula for microvascular wall shear force: ; in, parameter Defined at time node The dynamic value of microvascular wall shear force estimated by the time is expressed in Pascals or Daines per square centimeter. This parameter represents the internal frictional stress caused by the velocity gradient between fluid layers, and directly reflects the mechanical tearing strength of the fluid on endothelial cells and suspended exogenous therapeutic cells. parameter Define the current time node The apparent viscosity of microcirculatory blood is estimated by taking into account the Farin effect and the change in Zeta potential caused by the intervention of hydrogen and oxygen negative ions. This parameter is calculated by a high-order empirical mathematical polynomial composed of human body temperature, hematocrit calibration value, initial set value of plasma protein concentration and real-time hydrogen and oxygen negative ion input concentration. parameter Defined as a time node The autologous blood volume flow rate characteristic value of the targeted microcirculation bed is obtained by scaling the overall cardiac output according to the preset anatomical vascular bed distribution ratio constant. parameter Defined as the stepper motor of the injection pump at a time node The volumetric flow rate of the external nutrient medium solution containing exogenous cells injected into the circulatory system; parameter Defined as the dynamically calculated equivalent physical radius of the targeted microvessels, this radius will undergo a slight dynamic expansion due to the nonlinear effect of the vasodilatory effect of exogenous hydrogen and oxygen negative ions. Since this parameter is in the denominator and has a cubic exponent, its small changes will have a drastic physical impact on the overall shear force.

[0119] To ensure the mechanical integrity and biological activity of cells during infusion, the non-volatile safe zone in the system memory is pre-loaded with the physical shear limit constant for cell membrane rupture.

[0120] The system uses this limiting constant as a baseline upper limit and superimposes the dynamic oxygen uptake feedback parameters continuously monitored in steps two and three to construct a multidimensional nonlinear constraint feedback control law equation. This equation aims to calculate the infusion pump motor propulsion command that maximizes infusion efficiency during the oxygen dividend period without rupturing the cell membrane. ; in, parameter Defined as the system at time node The control pulse frequency command value is generated and sent to the stepper motor driver of the precision injection pump. The pulse frequency directly determines the instantaneous physical injection speed of the liquid through the reduction ratio of the transmission mechanism. parameter Defined as a system-preset pulse frequency conversion proportional physical constant, used to linearly map the hydrodynamic difference in Pascal units to the frequency dimension of the motor microstep control pulse; parameter Defined as the critical wall shear force constant at which the phospholipid bilayer membrane structure of exogenously treated cells physically breaks (calibrated by in vitro fluid tensile fracture experiments). parameter Defined as the current dynamic value of microvascular wall shear force obtained from the above estimation; parameter It represents an exponential function with the natural constant as its base, and utilizes its nonlinear decay characteristics to enhance the robust constraint capability of the system. parameter Defined as the physical adjustment coefficient for oxygen uptake rate fluctuation sensitivity, it is used to control the degree of drastic pump speed adjustment caused by small fluctuations in oxygen consumption; parameter The current continuously transmitted real-time dynamic oxygen uptake rate is a dimensionless value. parameter A mathematical threshold constant for the upper limit of safe oxygen uptake rate to prevent oxygen consumption competition.

[0121] Through the aforementioned extraction and precise calculation of underlying microscopic physical parameters, the wall shear force in the microenvironment is... Gradually approaching the physical danger threshold Or the dynamic oxygen uptake rate in the microcirculation When a rebound trend emerges under external stimuli, the fluid dynamics difference term and the exponential decay term based on the natural constant in the formula will simultaneously produce a strong mathematical constraint response.

[0122] These two restraining forces will quickly turn The command value is lowered. Upon receiving the command to reduce the pulse frequency, the rotor angular velocity of the stepper motor in the syringe pump decreases instantaneously, physically slowing down the absolute velocity of the exogenous cell suspension input. The reduced flow rate causes a decrease in the fluid shear rate within the microcirculation bed, and the wall shear force decreases.

[0123] At the same time, reducing the amount of cell input per unit time allows the microenvironment sufficient physical time for the diversion and reconstruction of local blood flow and the physical diffusion and replenishment of hydrogen and oxygen negative ions.

[0124] Conversely, if the wall shear force margin is sufficient and the oxygen uptake rate is extremely low, it means that this is an excellent time for physical introduction. The control equation will output a high pulse frequency command, and the infusion pump will operate stably within the set maximum rated propulsion rate range.

[0125] Step 5, Mathematical evaluation of post-intervention effects: Based on the dynamic oxygen uptake rate and cardiac output before and after the intervention, the combined intervention benefit index is calculated from the data stream. Combined with the individualized intervention effect time decay constant, the absolute physical time point for the next recommended intervention is deduced. When the joint intervention benefit index is less than or equal to the mathematical constant of the benefit safety lower limit, the system determines that the joint intervention has not reached the basic maintenance benefit level of microcirculation. The system then sets the next recommended intervention absolute physical time point to the physical time point corresponding to the sum of the current absolute calendar physical timestamp and the preset shortest retest interval, and generates a reassessment prompt message.

[0126] After completing the combined physical introduction and regulatory intervention of exogenous therapeutic cells and hydrogen and oxygen negative ions, this step constructs an evaluation system based on the massive amount of continuously recorded time-series physiological underlying characteristic data.

[0127] This system uses discrete time series integration and classical pharmacokinetic trends to quantify the substantial physical improvement of the intervention's effect on the subjects' circulatory system's oxygen-carrying capacity.

[0128] Based on the decay model of exogenous cell residence metabolism and the physical half-life of in vivo antioxidants, the system automatically calculates the personalized health management tracking schedule for the next cycle, thereby completing the reconstruction of the entire data link in medical informatics.

[0129] When the combined intervention reaches the set treatment dose and the main control unit sends a hardware stop command to shut down the external precision injection pump and hydrogen-oxygen negative ion generator hardware, the system's multimodal sensor array will not be powered off.

[0130] Instead, the system will automatically enter the set resting observation physical time window (e.g., 120 minutes). During this period, in order to prevent sensor baseline drift caused by minor postural changes in the subject after prolonged intervention, the system first performs a zero-phase digital filtering and baseline physical reset procedure.

[0131] By capturing stable low-frequency components in impedance cardiography and near-infrared spectral signals, the system uses a moving average algorithm to recalibrate the static impedance constant and the light absorption background constant. Then, it maintains the original high-speed data sampling rate of more than 100 times per second and continuously collects and outputs the dynamic oxygen uptake rate sequence, cardiac output sequence, and deep tissue oxygenation index sequence of the subject in the autonomous recovery state after being removed from external physical intervention.

[0132] The system's core processing unit extracts high-resolution data arrays from three key time periods completely and without loss from locally mounted high-capacity non-volatile flash memory storage media (such as NAND-based solid-state storage chips): Baseline resting period data recorded before intervention initiation, dynamic controlled pressure drop period data during full-power operation of the joint intervention equipment, and recovery resting period data after intervention cessation.

[0133] Based on these high-resolution time-domain data arrays, the system first constructs a mathematical time integral index to measure the "gain of oxygen consumption competition avoidance".

[0134] The system needs to calculate the difference in the two-dimensional physical envelope area between the high baseline oxygen uptake rate and the actual controlled oxygen uptake rate during the entire intervention period.

[0135] Since the data collected by the system are discrete time series points, the system cannot use continuous integration. Therefore, the core of the operation is deployed with a discrete numerical integration algorithm based on the composite Simpson's rule or the high-precision trapezoidal quadrature formula.

[0136] By algebraically summing the area micro-elements of millions of discrete time intervals, the total oxygen consumption that is reduced within the entire physical intervention time window can be accurately calculated.

[0137] The system retrieves cardiac output data before and after intervention. In order to eliminate the periodic fluctuations in cardiac output caused by sinus arrhythmia due to natural breathing, the system applies a low-pass filter with a cutoff frequency lower than the lower limit of respiratory rate to the cardiac output sequence, extracts the stable mean value reflecting the basic function of the heart, and then calculates the dimensionless ratio index reflecting the degree of improvement in the physical work of the cardiovascular dynamic system.

[0138] By combining these two quantitative indicators, the system employs a purely mathematical structure of weighted algebraic summation to output a comprehensive quantitative parameter, the joint intervention benefit index, calculated as follows: ; in, parameter Defined as the comprehensive quantitative evaluation index of the combined health management intervention effect, which is ultimately calculated, this value directly reflects the extent to which a single intervention improves the physical environment of the subject's circulatory microenvironment. parameter Defined as a mathematical weighting coefficient preset by the system for the area of ​​oxygen consumption pressure drop in microcirculation, this constant is statically calibrated based on the physical importance constant of human microcirculation metabolism; parameter With parameters These are defined as the absolute physical timestamps on the timeline at the official start-up and shutdown of the joint physical intervention equipment; parameter Defined as a stable mathematical constant of baseline oxygen uptake rate determined by averaging over a long period of time before intervention; parameter This is a time series of actual dynamic oxygen uptake rates continuously recorded during the intervention period; parameter Defined as a mathematical weighting coefficient preset by the system for the magnitude of improvement in macrocirculatory hemodynamics; parameter Defined as the mean value of the baseline cardiac output capacity characteristic obtained by digital low-pass filtering during the resting period before intervention; parameter Defined as the mean value of cardiac output after stabilization during the resting observation period following the intervention.

[0139] Obtain quantification After the index is reached, the system does not use the fixed countdown reminder mode found in conventional medical software. Instead, it introduces a time-domain prediction mathematical model based on the physical laws of metabolic decay in the microenvironment.

[0140] Because the exogenous therapeutic cells reside in the microvessels of the host, have a biochemical paracrine effect, and the free radical scavenging ability triggered by high concentrations of hydrogen and oxygen negative ions in the body, they all follow a specific physical half-life natural decay curve.

[0141] The system uses the benefit index calculated from this intervention as the initial high-potential energy boundary condition, and substitutes it into the classical first-order linear ordinary differential physics decay equation ( Solve for it.

[0142] To ensure high accuracy and individualization of decay prediction, the system does not use a uniform coarse time constant, but instead constructs a set of individual basic thermodynamic metabolic rate estimation sub-models.

[0143] The system first retrieves the subject's absolute physical height ( ),weight( ) and age ( The basal metabolic rate constant of the subjects was calculated using the modified Harris-Benedict thermodynamic empirical formula (or the DuBois formula based on body surface area).

[0144] The system is based on the formula Calculate the time decay constant of the individualized intervention effect; in, parameter Defined as the theoretical half-life constant of exogenous cells, determined by the quality control data of cell preparations or publicly available literature, for example, 14 days; parameter Defined as the subject's basal metabolic rate constant; parameter Defined as the average basal metabolic rate of the reference population.

[0145] Individuals with higher metabolic rates exhibit faster cellular consumption and antioxidant clearance. The larger the absolute value.

[0146] The system sets a mathematical constant representing the maintenance benefit safety lower limit of the organization's basic microcirculation needs. By solving the above-mentioned exponential decay model with individual characteristics, it calculates the precise time span required for the initial comprehensive quantitative evaluation index to naturally decrease to the above-mentioned safety lower limit mathematical constant over the course of physical time.

[0147] The system performs a mathematical addition on this time span value and the absolute calendar time of the current completed intervention to deduce the precise calendar date and time when the subject should undergo the next data collection follow-up or start the next round of equivalent combined physical intervention: ; in, parameter Defined as the absolute physical time point at which the system's final output is written into the subject's electronic health record database for the next recommended intervention or data retest; parameter Defined as the current absolute calendar physical timestamp of the current completed effect assessment procedure; parameter Defined as the time decay constant of the individualized intervention effect, calculated based on the subject's body surface thermodynamic parameters and basal metabolic rate; parameter It represents the logarithmic function with the natural constant as its base, used to solve the inverse process of the exponential decay equation; parameter To obtain the single joint intervention benefit index; parameter Defined as a mathematical constant representing the lower limit of the safety of the microcirculation microenvironment in maintaining normal physiological function without irreversible damage.

[0148] The system encapsulates all the data arrays containing physical units, all the original time-series waveforms generated during the calculation and deduction process, the exponential results calculated by the dynamic evaluation formula, and the dynamic time management nodes derived from the formula at a high level of structure.

[0149] The system employs a symmetric encryption algorithm with high physical complexity (such as the AES-256 standard) to perform bit-level mathematical obfuscation and diffusion calculations on discrete physiological data through shift registers and nonlinear substitution boxes (S-Boxes) to generate ciphertext payloads with tamper-resistant capabilities.

[0150] Through a dedicated Internet of Medical Technology (IoMT) physical communication protocol layer, it is pushed to the subject's local health management display terminal or cloud medical data backup server.

[0151] The above description is merely a specific embodiment of this application, but the scope of protection of this application is not limited thereto. Any variations or substitutions that can be easily conceived by those skilled in the art within the scope of the technology disclosed in this application should be included within the scope of protection of this application. Therefore, the scope of protection of this application should be determined by the scope of the claims.

Claims

1. A health management method combining cell therapy with hydrogen and oxygen negative ions to regulate the circulatory system, characterized in that, include: The data stream is calculated by obtaining the absorbance ratio parameter of dual-wavelength transmitted light intensity, tissue oxygenation index and physical characteristics of microvascular dilation, and the cardiac output is derived from the instantaneous heart rate sequence and the single ventricular stroke volume. Based on the ratio parameter of absorbance of dual-wavelength transmitted light intensity and tissue oxygenation index, the oxygen content of arterial blood and mixed venous blood is estimated, and the dynamic oxygen uptake rate is calculated by combining cardiac output with the data stream. When the dynamic oxygen uptake rate is greater than the preset safe oxygen uptake rate upper limit mathematical threshold, hydrogen and oxygen negative ions are output, and when the dynamic oxygen uptake rate is lower than the preset safe oxygen uptake rate upper limit mathematical threshold, a cell therapy intervention time window opening trigger signal is generated. After receiving the cell therapy intervention time window opening trigger signal, the dynamic value of microvascular wall shear force is estimated by calculating the data stream from cardiac output and the physical characteristic parameters of microvascular dilation. Combined with the dynamic oxygen uptake rate, the motor propulsion control pulse frequency command value is obtained and the precision injection pump is controlled. Based on the dynamic oxygen uptake rate and cardiac output data stream before and after the intervention, a joint intervention benefit index is derived. Combined with the individualized intervention effect time decay constant, the next recommended absolute physical time point for intervention is deduced.

2. The method for health management of the circulatory system by combining cell therapy with hydrogen and oxygen negative ions according to claim 1, characterized in that, The process of obtaining the ratio of the characteristic absorbance of the dual-wavelength transmitted light is as follows: The first center wavelength excitation source in the red light spectrum band and the second center wavelength excitation source in the near-infrared light spectrum band are driven alternately using time-division multiplexing technology. The transmitted light intensity is captured by a photodetector and the AC light intensity component and DC light intensity component are extracted by a low-noise transimpedance amplifier and an analog-to-digital conversion channel. The process of obtaining the physical characteristics of microvascular dilation is as follows: Extracted from the characteristics of photoelectric pulse waves composed of AC light intensity components and DC light intensity components; The process of obtaining the tissue oxygenation index is as follows: By using a broadband near-infrared light source emitter and multiple photodetectors arranged at equal intervals along the same straight line, the spatial differential attenuation rate of the received light intensity attenuation gradient is calculated. Combined with the specific absorption peaks of oxyhemoglobin and deoxyhemoglobin, the spectral absorption coefficient is linearly unmixed to calculate the tissue oxygenation index.

3. The method for health management of the circulatory system by combining cell therapy with hydrogen and oxygen negative ions according to claim 2, characterized in that, The process of calculating cardiac output from instantaneous heart rate sequence and single ventricular stroke volume to extrapolate the data stream is as follows: A high-frequency constant current micro-alternating current is injected into the pleural cavity and the voltage drop fluctuation on the surface of the pleural cavity is captured. A cascaded digital bandpass filter is used to eliminate baseline drift, and the waveform of the pleural cavity impedance changing with time after eliminating baseline drift is extracted. First-order time differential mathematical operation is performed on the waveform of thoracic impedance change over time to generate the time-domain characteristic curve of impedance change rate, obtain the amplitude of the absolute maximum peak point and the physical time of left ventricular ejection, and multiply them with the basic resistivity constant parameter of human standard blood to obtain the single ventricular stroke volume. The instantaneous heart rate sequence is calculated by obtaining the time interval between adjacent ejection peak points, and the instantaneous heart rate sequence is multiplied by the corresponding timestamp of a single ventricular stroke to generate a cardiac output estimation data stream.

4. The method for health management of the circulatory system by combining cell therapy with hydrogen and oxygen negative ions according to claim 1, characterized in that, The process of calculating arterial blood oxygen content and mixed venous blood oxygen content is as follows: The ratio of absorbance of dual-wavelength transmitted light intensity is mapped to the percentage of non-invasive arterial blood oxygen saturation by a second-order polynomial physical calibration equation, and the arterial blood oxygen content is obtained by combining the hemoglobin gram calibration value and physical dissolved oxygen partial pressure. By introducing a fixed vascular bed venous weight coefficient to scale the tissue oxygenation index, the percentage parameter of mixed venous blood oxygen saturation is extracted. The mixed venous blood oxygen content is then obtained by combining the hemoglobin gram calibration value and the physical dissolved oxygen partial pressure.

5. The method for health management of the circulatory system by combining cell therapy with hydrogen and oxygen negative ions according to claim 4, characterized in that, The process of calculating dynamic oxygen uptake rate is as follows: Based on the principle of physical diffusion, the oxygen delivery rate is obtained by multiplying the cardiac output data stream by the arterial blood oxygen content; the difference between the arterial blood oxygen content and the mixed venous blood oxygen content is calculated, and the difference is multiplied by the cardiac output data stream to obtain the oxygen consumption. The dynamic oxygen uptake rate is obtained by dividing the oxygen consumption by the oxygen delivery rate.

6. The method for health management of the circulatory system by combining cell therapy with hydrogen and oxygen negative ions according to claim 1, characterized in that, When the dynamic oxygen uptake rate is greater than the preset safe oxygen uptake rate upper limit mathematical threshold, hydrogen and oxygen negative ions are output; when the dynamic oxygen uptake rate is lower than the preset safe oxygen uptake rate upper limit mathematical threshold, a cell therapy intervention time window opening trigger signal is generated, specifically including: The system generates hydrogen by regulating the amplitude of the DC driving voltage applied to the electrodes on both sides of the electrolysis chamber, and at the same time applies a negative polarity DC pulse high voltage to the high voltage corona discharge needle array to generate a negative oxygen ion flow. The hydrogen and negative oxygen ion flow are physically mixed by a mass flow controller and output as hydrogen-oxygen negative ions. The prerequisites for generating a trigger signal to open the intervention time window for cell therapy include: Set a continuous time window threshold constant. Only when the dynamic oxygen uptake rate is continuously lower than the preset safe oxygen uptake rate upper limit mathematical threshold and this state is maintained for more than the continuous time window threshold constant on the time axis, will the cell therapy intervention time window opening trigger signal action be executed.

7. The method for health management of the circulatory system by combining cell therapy with hydrogen and oxygen negative ions according to claim 6, characterized in that, The formula for calculating the DC drive voltage amplitude and the characteristic value of the drive voltage command for the negative polarity DC pulse high voltage is as follows: ； in, This is the characteristic value of the drive voltage command; A proportional gain constant established to address the current oxygen uptake deviation; Dynamic oxygen uptake rate; The mathematical threshold for the preset safe oxygen uptake rate; The physical constant of the integral gain; The self-parameter of continuous virtual physical time; The theoretical constant for the physical gain of charge caused by a single negative ion in a unit volume of blood; To compensate for the physical constant of the intervention dose.

8. The method for health management of the circulatory system by combining cell therapy with hydrogen and oxygen negative ions according to claim 1, characterized in that, When estimating the dynamic values ​​of shear force on the microvascular wall: The apparent viscosity of microcirculatory blood was extracted and estimated, and the data stream was combined with cardiac output to calculate the characteristic value of autologous blood volume flow rate of the targeted microcirculatory bed. The volumetric flow rate of the external nutrient medium solution containing exogenous cells injected into the circulatory system by the precision injection pump was also obtained. The dynamic value of microvascular wall shear force is obtained by multiplying the estimated apparent viscosity by the sum of the characteristic value of autologous blood volumetric flow rate and volumetric flow rate, and dividing by the cubic parameter of the dynamically estimated equivalent physical radius affected by the physical characteristic parameters of microvascular dilation.

9. The method for health management of the circulatory system by combining cell therapy with hydrogen and oxygen negative ions according to claim 8, characterized in that, The motor propulsion control pulse frequency command value is obtained using the following formula: ； in, This refers to the command value for the motor propulsion control pulse frequency. This is the physical constant for the pulse frequency conversion ratio; It is the critical wall shear force constant for the physical rupture of the phospholipid bilayer membrane structure; This represents the dynamic value of shear force on the microvascular wall. It is an exponential function with the natural constant as its base; The physical adjustment coefficient for oxygen uptake rate fluctuation sensitivity; Dynamic oxygen uptake rate; This is a preset mathematical threshold for the upper limit of safe oxygen uptake.

10. The method for health management of the circulatory system by combining cell therapy with hydrogen and oxygen negative ions according to claim 1, characterized in that, Based on the dynamic oxygen uptake rate and cardiac output data stream before and after the intervention, a joint intervention benefit index is derived. Combined with the individualized intervention effect time decay constant, the next recommended absolute physical time point for intervention is deduced, specifically including: The discrete numerical integration algorithm was used to perform algebraic accumulation of area micro-elements on discrete time series points reflecting the decrease in dynamic oxygen uptake rate. Combined with the improvement in large circulation hemodynamics obtained from the data stream based on cardiac output, the combined intervention benefit index was calculated. The absolute physical height, weight and age are extracted, the basal metabolic rate constant is calculated using the basic thermodynamic empirical formula, and the individualized intervention effect time decay constant is output by mapping through the linear scaling operator. Based on the preset time-domain prediction mathematical model, the absolute physical time point of the next recommended intervention is deduced using the following formula: ； in, The absolute physical time point for the next recommended intervention; The current absolute calendar physical timestamp; This represents the time decay constant of the individualized intervention effect; It is a logarithmic function with the natural constant as its base; For the joint intervention effectiveness index; This is a mathematical constant representing the lower limit of efficiency and safety.

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