A multi-spectrum phase modulation bone joint magnetic therapy system

Abstract

This invention relates to the field of advanced medical equipment and instrument manufacturing, and more particularly to a multi-spectral phase-modulated joint magnetic therapy system, comprising a main control unit, a spectrum construction unit, a phase unrolling unit, a migration scheduling unit, a magnetic drive unit, and a magnetic stimulation probe. The main control unit generates multi-frequency stimulation sequence parameters; the spectrum construction unit partitions the multi-frequency stimulation signal; the phase unrolling unit applies progressive phase modulation to each spectrum region; the migration scheduling unit performs temporal reconstruction of each spectrum region and forms a migration sequence; and the magnetic drive unit drives the magnetic stimulation probe to output a corresponding magnetic field structure according to the migration sequence. This invention, by constructing a migration stimulation mode based on spectrum partitioning and phase unrolling, can change the effect structure of multi-frequency magnetic fields within human tissue, reduce the influence of tissue differences on phase relationships, and improve the stability of stimulation distribution and treatment consistency among different individuals.

Description

Technical Field

[0001] This invention relates to the field of advanced medical equipment and instrument manufacturing, and more specifically to a multi-spectral phase-modulated bone and joint magnetic therapy system. Background Technology

[0002] Magnetic stimulation (MS) therapy utilizes changing magnetic fields to generate induced currents in human tissues, thereby producing electrophysiological stimulation to nerve and muscle tissues. It has been increasingly applied in the adjunctive treatment of bone and joint pain. Existing bone and joint magnetic therapy devices typically use a main unit to drive a magnetic stimulation coil to generate a pulsed magnetic field. This pulsed magnetic field induces eddy currents in human tissues, achieving electrophysiological stimulation of nerves, muscles, and blood vessels. To improve the stimulation effect and avoid adaptation phenomena caused by single-frequency stimulation, some magnetic therapy systems employ multi-spectral magnetic field output, creating a composite magnetic stimulation waveform by superimposing multiple pulse signals of different frequencies. Furthermore, to regulate the synergistic effect between different frequency signals, some systems further introduce phase modulation technology. By controlling the phase difference between each frequency signal, multiple frequency components form a specific superposition pattern in time, aiming to create a more complex electromagnetic stimulation structure in the target tissue area, thereby enhancing the stimulation effect on nerves and tissues in the bone and joint region.

[0003] However, because human tissues are composed of various media such as skin, fat, muscle, and bone, the electrical conductivity and electromagnetic properties of each tissue differ significantly. In practical applications, multi-frequency magnetic fields experience varying degrees of attenuation and propagation delay during propagation, and the propagation paths and speeds of different frequency components within the tissue vary. In this situation, although the magnetic therapy system sets a fixed phase relationship for multiple frequency signals at the output end, the phase relationship of each frequency signal changes as the magnetic field enters the human tissue and propagates to the bone and joint areas, causing distortion of the originally set phase structure in the target tissue area. Since the synergistic effect of multi-frequency magnetic stimulation depends on the stable phase relationship between each frequency component, when the phase structure changes within the tissue, the actual stimulation spectrum structure obtained in the target area will be difficult to maintain the preset state. This affects the consistency and stability of the magnetic therapy system, resulting in significant differences in stimulation effects between different treatment locations or patients of different body types. Summary of the Invention

[0004] To address the shortcomings of existing technologies, this invention discloses a multi-spectral phase-modulated bone and joint magnetic therapy system, aiming to solve the problems mentioned in the background art.

[0005] To achieve the above-mentioned technical effects, the present invention adopts the following technical solution: A multi-spectral phase-modulated bone and joint magnetic therapy system, the system comprising a main control unit, a spectrum construction unit, a phase unfolding unit, a migration scheduling unit, a magnetic drive unit, and a magnetic stimulation probe; The main control unit is used to generate a multi-frequency stimulation sequence parameter set, which includes spectral partitioning parameters, phase progression parameters, and migration sequence parameters. The spectrum construction unit is used to divide the multi-frequency stimulus sequence into frequency intervals based on the spectrum partitioning parameters, forming at least two independent spectrum regions, and establishing a corresponding frequency reference phase for each spectrum region. The phase unrolling unit is used to perform progressive phase shifting processing on the frequency reference phase of each spectral region according to the phase advancement parameter within a continuous stimulation cycle, generating a phase advancement sequence so that each spectral region forms a gradually changing phase structure in a continuous cycle. The migration scheduling unit is used to perform temporal reconstruction of the phase progression sequence according to the migration sequence parameters, establish the sequential activation relationship of the spectral region in the continuous stimulation cycle, and form a spectral migration sequence unfolding along the time axis. The magnetic drive unit is used to generate a corresponding pulse drive current sequence according to the spectrum migration sequence and apply it to the magnetic stimulation coil; The magnetic stimulation probe is electrically connected to the magnetic drive unit. The magnetic stimulation probe contains a magnetic stimulation coil. Under the action of the pulse drive current sequence, the magnetic stimulation coil outputs a corresponding temporal magnetic field structure. The temporal magnetic field structure forms a magnetic stimulation field distribution in the human bone and joint region that unfolds according to the spectral migration sequence.

[0006] As a further technical solution of the present invention, the process of generating the multi-frequency stimulus sequence parameter set includes: The preset frequency range is divided into multiple continuous frequency intervals, and the center frequency of each frequency interval is taken as the reference frequency value. Calculate the corresponding period length based on each reference frequency value, and sort each frequency interval in descending order of period length to obtain the spectrum partition parameters; Calculate the period difference between adjacent frequency intervals after sorting, and normalize each period difference based on the maximum period difference to obtain a normalized difference sequence. Based on the normalized difference sequence, the phase advance angle value between each adjacent frequency interval is calculated according to a preset linear function relationship to generate phase advance parameters. The first frequency interval in the ordered frequency sequence is taken as the starting interval. Time windows are assigned to each frequency interval in the order of the ordered frequency sequence. The length of the time window for each frequency interval is calculated by the corresponding normalized difference through a preset scaling factor, forming a continuous and non-overlapping migration sequence parameter.

[0007] As a further technical solution of the present invention, the spectrum construction unit includes a frequency analysis subunit, a period mapping subunit, an interval division subunit, and a reference phase generation subunit. The frequency analysis subunit is used to extract each frequency component in the multi-frequency stimulus sequence and form a frequency set. The period mapping subunit is used to perform period calculation on each frequency component in the frequency set to obtain a corresponding period parameter set, and calculate the period difference of each period parameter relative to the reference period with reference to the period corresponding to a preset reference frequency. The interval division subunit is used to sort the frequency set based on the period difference and divide it according to the hierarchical interval of the period difference, so that each frequency component in the same spectrum region satisfies that the period difference is within the same difference interval, forming multiple spectrum regions. The reference phase generation subunit is used to select a reference frequency component for each spectrum region, and use the initial phase of the reference frequency component as the reference phase of the spectrum region. At the same time, it establishes a phase mapping relationship between the frequency component and the reference phase based on the period difference of each frequency component in the spectrum region relative to the reference frequency component.

[0008] As a further technical solution of the present invention, the spectrum construction unit further includes: The time base generation subunit is used to determine the unified time base period based on the period parameter set, and to map the period of the reference frequency component in each spectrum region to the unified time base period to obtain the standardized period parameters corresponding to each spectrum region. The interval constraint subunit is used to calculate the time occupancy length of each spectrum region within the unified time reference period based on the standardized period parameters of each spectrum region, and to allocate time intervals to each spectrum region according to the time occupancy length, so that only one spectrum region is in the active interval at any given time. At the same time, the switching boundary between adjacent spectrum regions is determined by the difference in their standardized period parameters, forming multiple non-overlapping spectrum interval sequences on the time axis.

[0009] As a further technical solution of the present invention, the working process of the phase unrolling unit includes: The period difference corresponding to the frequency component in each frequency region is processed in a hierarchical manner, the period difference is mapped to a preset difference interval, and a corresponding phase step value is assigned to each difference interval to form a phase step set. Using the reference phase of each spectral region as the initial phase, the frequency components are iteratively calculated cycle by cycle within a continuous stimulation period. The phase value in the nth cycle is obtained by adding the phase value of the (n-1)th cycle to the corresponding phase increment value. After each cycle calculation, a period modulo operation is performed on the obtained phase value to limit the phase value within a preset phase range, and the phase sequence corresponding to each frequency component in each cycle is obtained.

[0010] As a further technical solution of the present invention, the phase expansion unit is also used to convert the phase sequence corresponding to each frequency component in each period into a time sequence, the process including: Based on the period parameters corresponding to each frequency component, the phase values ​​in the phase sequence are proportionally converted into time offsets relative to the start time of the current period. The time offset is equal to the product of the phase value and the corresponding period divided by a preset phase period range. Each cycle is divided into multiple consecutive time units, and the time unit index corresponding to each frequency component is determined according to the time offset, so that each phase value corresponds to a unique time unit position. The frequency components are sorted by time unit index, and time units belonging to the same spectrum region are aggregated to generate the time activation sequence corresponding to each spectrum region in a continuous period.

[0011] As a further technical solution of the present invention, the working process of the migration scheduling unit includes: Based on the time activation sequence corresponding to each spectrum region, the time unit index set of each spectrum region in each period is extracted, and the center activation time of each spectrum region in the current period is calculated. The center activation time is the weighted average of the corresponding time unit index. Scheduling priority parameters are constructed for each spectrum region. These parameters are obtained by coupling the center activation time, standardized period parameters, and period difference of each spectrum region. The calculation formula is as follows: in, Indicates the first Scheduling priority parameters for each spectrum region; Indicates the first The central activation time of each spectrum region; Indicates a unified time base period; Indicates the first The period difference of each frequency region relative to the reference frequency component; Indicates the first The number of frequency components contained in each spectrum region; The preset weighting coefficients satisfy the following conditions: ; The spectrum regions are sorted according to the scheduling priority parameters, and the activation order of the spectrum regions in the current period is generated based on the sorting results. Between adjacent cycles, the activation order of the spectrum region is subjected to continuity constraint processing, so that the activation start position of the spectrum region in the later cycle and the activation end position of the spectrum region in the previous cycle maintain the minimum time interval, forming a continuous spectrum migration sequence across cycles.

[0012] As a further technical solution of the present invention, the migration scheduling unit is also used to allocate time windows corresponding to the activation order of each spectrum region, and the working process includes: Extract the period difference and standardized period parameter corresponding to each spectral region, and perform nonlinear coupling calculations to construct a time window allocation weight parameter. The calculation formula is as follows: in, Indicates the first Weighting is assigned to each spectrum region within a time window. Indicates the first The period difference of each frequency region relative to the reference frequency component; Indicates the first Standardized periodic parameters for each spectrum region; To preset nonlinear exponential coefficients, and ; Indicates the total number of spectrum regions; Based on the weighting parameters assigned within the time window, a unified time base period will be established. The frequency spectrum is divided into multiple consecutive time windows, with the length of each time window corresponding to a specific frequency region. ; The time windows are arranged sequentially according to the activation order of the spectrum regions, so that each spectrum region occupies the corresponding time window in sequence within a unified time base period, and any two adjacent time windows are connected end to end without overlap, forming a complete time occupancy structure sequence.

[0013] As a further technical solution of the present invention, the migration scheduling unit is also used to construct a continuous transition interval between time windows of adjacent spectrum regions, and the working process includes: In two adjacent spectral regions arranged in the activation order and At the boundary of the time window, the transition time interval is divided according to the length of the time window of the corresponding two frequency regions. The formula expression is: in, Indicates the spectrum region With the spectrum region The length of the transition time interval between them; Representing the spectrum regions and Time window length; This is a preset proportional coefficient, and ; During the transition time interval, for the spectrum region With the spectrum region The time occupancy weight is continuously adjusted, and the frequency spectrum is adjusted through a weight change function. The occupancy weight is gradually reduced from 1 to 0, while the spectrum region is... The weight of the occupancy gradually increases from 0 to 1, and the formula is as follows: in, They represent the times at time 1 and 2 respectively. At that time, the spectrum region With the spectrum region Time occupancy weight; Indicates the start time of the transition time interval; It is a non-linear adjustment index, and ; Within the transition time interval, the time activation sequence of the corresponding spectrum region is reconstructed according to the time occupancy weight, so that only one spectrum region is active at any given time, and the activation attribution of the spectrum region is switched according to the magnitude of the time occupancy weight, thus forming a spectrum migration path within the continuous stimulation cycle.

[0014] As a further technical solution of the present invention, the working process of the magnetic drive unit includes: Based on the spectral region identifiers corresponding to each time unit in the spectral migration sequence, a mapping relationship between time units and driving current parameters is established, and a corresponding pulse driving current parameter set is generated for each time unit. The pulse driving current parameter set includes current amplitude. Pulse width and pulse interval ; Wherein, the current amplitude The calculation is performed by coupling the standardized periodic parameters and time occupancy weights of the corresponding spectrum region. The calculation formula is as follows: in, Indicates time The magnitude of the driving current; Indicates the preset reference current amplitude; The standardized periodic parameter represents the frequency range to which the current time unit belongs; Indicates a unified time base period; Indicates the corresponding spectral region at time Time occupancy weight; For the preset exponential coefficient, and ; The pulse width With pulse interval The calculation is performed in segments based on the length of the time unit and the period parameter of the corresponding spectrum region. The number of pulses in each time unit satisfies the output frequency that is consistent with the period of the spectrum region. Between adjacent time units, the current amplitude Continuity constraints are applied to ensure that the rate of change of current between adjacent time points does not exceed a preset threshold. ,satisfy ,in, Indicates the interval between adjacent time units; Based on the set of pulse drive current parameters, the magnetic stimulation coil is switched on and off by the drive control circuit, and the pulse drive current is output sequentially in a time sequence.

[0015] Based on the above technical solution, the positive and beneficial effects of the present invention are as follows: This scheme transforms the multi-frequency stimulation signal from a fixed-phase superposition structure to a temporally unfolded structure based on spectral partitioning. Combined with phase-progressive modulation and migration scheduling control, it enables different frequency components to form a continuously unfolded stimulation sequence over time. This alters the way multi-frequency magnetic fields act within human tissue, reducing the disruption of phase relationships caused by propagation delays due to differences in tissue conductivity. This suppresses the problem of spectral structure distortion in the target region from the perspective of stimulation formation mechanism. Furthermore, by constructing a stimulation field migration mode with sequential activation of spectral regions, this invention enables magnetic stimulation to form a continuously varying induced current distribution over time in the bone and joint region. This avoids local interference caused by the concentrated superposition of multi-frequency signals at the same moment, resulting in continuous coverage of the stimulation area within the tissue. This helps maintain the uniformity of stimulation intensity distribution within the target region.

[0016] Secondly, since the stimulation field unfolds within the tissue in the form of a migration sequence, this invention can reduce the influence of differences in electromagnetic propagation under different body sizes and tissue structures on the stimulation results, making the stimulation pattern formed under the same control parameters more consistent among different individuals, while improving the stability and adaptability of the magnetic therapy system in the process of bone and joint treatment. Attached Figure Description

[0017] To more clearly illustrate the technical solutions in the embodiments of the present invention or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort, wherein: Figure 1 This is a schematic diagram of the principle framework of the present invention; Figure 2 This is a schematic diagram illustrating the spatial distribution of the magnetic field of the present invention over time. Figure 3 This is a schematic diagram illustrating the change of the magnetic field center position over time according to the present invention; Figure 4 This is a schematic diagram of the spectrum division and phase recursion expansion based on the period difference hierarchical control. The diagram is labeled as follows: 100, main control unit; 200, spectrum construction unit; 300, phase unfolding unit; 400, migration scheduling unit; 500, magnetic drive unit; 600, magnetic stimulation probe. Detailed Implementation

[0018] To make the objectives, technical solutions, and advantages of the embodiments of this application clearer, the technical solutions of the embodiments of this invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of this invention, and not all embodiments. Based on the embodiments of this invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this invention.

[0019] Unless otherwise defined, all techniques and scientific methods used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this application belongs. The descriptions herein are for the purpose of illustrating particular embodiments only and are not intended to limit the invention. The terms "and / or" as used herein include any and all combinations of one or more of the associated listed items.

[0020] In a practical application of a multi-spectral phase-modulated joint magnetic therapy system, the device adopts a mobile structure, with the main unit mounted on a caster base for easy movement in the treatment environment. The main unit integrates control circuitry, a power module, and a power drive circuit. An adjustable support arm connects the magnetic drive unit 500 to the top of the main unit. The probe can be fixed to the surface of a human joint, such as the knee or shoulder joint, ensuring the center of the coil is aligned with the target treatment area. The main unit and the probe are connected via a multi-core cable, which includes power conductors and control signal lines.

[0021] When using the device, the operator inputs the combination of stimulation frequencies and treatment time through the user interface. For example, a typical setup might involve inputting frequencies of 20Hz, 35Hz, and 50Hz, with a treatment cycle of 1 second. After system startup, the control program first divides this 1-second cycle into equally spaced discrete time slices, such as 1000 time slices, each lasting 1 millisecond. All subsequent control processes unfold progressively within this time slice sequence.

[0022] During the time progression, the system calculates the corresponding period based on the input frequency and determines the positional distribution of each frequency within the entire 1-second time range. Unlike conventional multi-frequency stimulation methods, the system does not output multiple frequency signals simultaneously within the same time slice. Instead, it selects only one frequency's spectral region as the current driving target within each time slice. Specifically, the system divides the frequencies into several groups based on the periodic relationship between them and assigns different time segments to different groups on the time axis, ensuring that each group appears sequentially in time.

[0023] For example, under the aforementioned parameters, the system may initially prioritize allocating frequency groups containing 20Hz and 35Hz, outputting pulsed currents of corresponding rhythms within the first few consecutive time slots. As time progresses, the system gradually reduces the number of time slots occupied by this frequency group while increasing the proportion of time slots occupied by the 50Hz frequency group, causing the dominant output frequency to gradually transition from low to high frequencies. Throughout this process, each time slot always corresponds to only one frequency group, ensuring that the current flowing through the coil at any given moment reflects only a single frequency structure.

[0024] The switching between frequencies is not abruptly completed at a single point in time, but rather a gradual transition over a continuous period. For example, during the alternation of two frequency groups, the system alternately allocates control of different frequency groups over several consecutive time slices. In the initial stage of the transition, the former frequency group still occupies the majority of time slices, while the latter frequency group occupies only a small number of time slices. As time progresses, the proportion of time slices occupied by the two gradually changes until the latter frequency group completely replaces the former. In this way, a continuously changing frequency distribution is formed on the time scale, while maintaining a single frequency output on a single time slice scale.

[0025] During the drive execution phase, the power drive circuit inside the host generates a pulsed current signal based on the frequency parameters corresponding to the current time slice. The pulse interval output by the drive circuit varies for different frequencies; for example, in a 20Hz operating state, the current repeats with a period of 50 milliseconds, while in a 50Hz state, it repeats with a period of 20 milliseconds. The current amplitude is adjusted according to the current stage in different time slices. During frequency group transitions, the current amplitude changes continuously, thus avoiding the impact caused by sudden current changes.

[0026] The pulsed current is transmitted to a coil within the magnetic drive unit 500 via connecting wires. The coil typically employs a multi-turn winding structure, coupled with insulation and heat dissipation design. Under the influence of the current, the coil generates a time-varying magnetic field in the surrounding space. Since the system outputs only a single frequency at any given time slice, the magnetic field exhibits a single-frequency characteristic on a microscopic time scale. However, on a macroscopic time scale, different frequencies appear sequentially and gradually transition, thus forming a stimulation process that varies along the time direction.

[0027] In actual operation, the system also monitors the output process in real time. A current detection module is installed in the drive circuit to sample the coil current and feed the detection results back to the control program. When the detected current deviates from the target value, the system adjusts the drive signal for subsequent time slices to ensure stable output. Simultaneously, a temperature detection element is installed inside the magnetic drive unit 500 to monitor the coil temperature. When the temperature reaches a set threshold, the system can appropriately reduce the current amplitude or adjust the time allocation to prevent overheating.

[0028] To verify the applicability of the system, in another set of implementation parameters, 15Hz, 25Hz, 40Hz, and 60Hz were selected as input frequencies, and the treatment cycle was set to 2 seconds. Under these conditions, the system also divided the time into equally spaced time slices and performed time allocation and transition processing for different frequencies throughout the cycle. The low-frequency portion occupied a longer time interval in the initial stage, while the high-frequency portion gradually increased its proportion in the subsequent stages. Smooth transitions were achieved through the redistribution of continuous time slices during the frequency group alternation process. Tests showed that the system could form a stable time distribution structure under different frequency combinations without requiring individual adjustments for specific frequency combinations.

[0029] As can be seen from its operation, this system does not simultaneously superimpose multiple frequency signals throughout the process. Instead, it segments and continuously transitions different frequencies along the time axis, allowing each frequency to act on the target area sequentially. In traditional methods, multi-frequency signals are usually output simultaneously in a superimposed form. Different frequencies are easily affected by tissue characteristics during propagation, resulting in phase changes and causing the actual effect to deviate from expectations. In this embodiment, since only a single frequency structure exists at any given time, there is no mutual superposition or interference between frequencies. Its propagation state in the tissue is more stable, and the continuous temporal distribution ensures that the overall stimulation process still retains multi-frequency characteristics.

[0030] In this implementation, an experiment was designed to verify the "period difference-driven time scheduling mechanism" of this scheme. Considering that the essential characteristic of traditional multi-frequency superposition methods is that each frequency component acts simultaneously within the same time period, thus forming a relatively stable superposition field distribution in space, this experiment did not directly use the final stimulus effect as the sole indicator, but instead introduced the "spatial distribution change during the time unfolding process" as an intermediate observation object. Specifically, 10 Hz, 15 Hz, 25 Hz, and 40 Hz were selected as the input frequency set, and 20 Hz was used as the reference frequency to calculate the period and obtain the period difference sequence. Based on this, a spectrum partition was constructed and a corresponding time scheduling sequence was generated. The control group used the same frequency set for direct superposition driving. Under the same driving current upper limit and coil structure conditions, the magnetic field distribution of the two methods in the same spatial region was synchronously acquired, and the magnetic field intensity changes of multiple spatial measurement points were recorded with a time resolution of 1 ms.

[0031] Please see the appendix Figure 2 The diagram illustrates the spatial distribution of the magnetic field over time. In traditional multi-frequency superposition methods, the magnetic field distribution remains largely consistent across different time sections, with the equivalent high-intensity regions aligned vertically and showing no significant spatial displacement. However, in this proposed scheme, the magnetic field distribution across different time sections exhibits a continuous spatial shift, with the high-intensity regions gradually moving along the spatial direction. There is partial overlap between adjacent time sections, forming a continuous migration trajectory. This phenomenon demonstrates that this scheme, through time scheduling and migration construction, transforms the originally simultaneously superimposed multi-frequency interaction into a spatially unfolding process along the time axis, enabling the magnetic stimulation field to exhibit controllable displacement characteristics in the time dimension.

[0032] During data processing, an equivalent stimulus center location is further constructed to characterize the overall spatial interaction state. This involves weighting the magnetic field strength at each measuring point to obtain the trajectory of the center location as it changes over time. Please refer to the appendix for details. Figure 3 The curve showing the change of the center position over time reveals that in the control group, the change in this position exhibits a stepped or approximately horizontal distribution, with discontinuous jumps between adjacent time points and a small overall displacement amplitude. In contrast, the curve for this scheme shows a continuous and smooth trend, gradually changing monotonically over time without any significant abrupt changes. Calculations based on the first-order difference of the center position change show that the mean square value of the velocity change in the control group is 2.3 mm / s². 2 In this scheme, the value is reduced to 0.6 mm / s. 2 This indicates that the spatial migration process has changed from discrete jumps to continuous changes, achieving greater controllability in the time dimension.

[0033] Based on this, to verify whether the migration process leads to a change in the actual spatial range of influence, statistics were compiled on the spatial points within the entire stimulation region that reached the threshold magnetic field strength. The experimental results are shown in the table below. Within the same time window, this scheme can cover more independent spatial locations: It can be seen that, under the time scheduling mechanism, the stimulus energy is no longer concentrated in a fixed spatial location, but is redistributed in the time dimension, thus forming a larger spatial coverage. Further analysis of the cumulative response intensity distribution of each measuring point throughout the entire time window shows that the response in the control group is concentrated in a few locations, with a standard deviation of 0.42, while in this scheme, the value is reduced to 0.18, indicating that the stimulus is more evenly distributed in space.

[0034] To eliminate the impact of time segmentation alone, further ablation experiments were conducted while keeping the frequency set unchanged. Specifically, the period difference driving mechanism was removed, retaining only simple time segmentation without constructing a continuous migration path. Experimental results showed that the spatial coverage in this case was 38%, significantly lower than the 55% of our proposed scheme. Furthermore, the corresponding spatial distribution exhibited discrete switching between different time periods, failing to form a continuous migration path. Figure 2 The continuous migration trajectory shown also lacks an attached curve indicating the change in its center position. Figure 3 The smooth, continuous characteristics shown indicate that the effectiveness of this scheme depends on the continuous migration structure formed under period difference driving, rather than being achieved through simple time scheduling.

[0035] Based on the above experimental process and changes, it can be seen that this scheme, by introducing the period difference as a unified driving variable, transforms the multi-frequency stimulation from "spatial superposition" to "temporal unfolding and continuous migration," thereby changing the spatial distribution of the magnetic field from static concentration to dynamic reconstruction. This not only achieves continuous and controllable movement of the stimulation center position but also significantly improves the spatial coverage and response uniformity, while reducing the degree of abrupt changes in the stimulation process. Compared with the traditional multi-frequency superposition method, it exhibits more significant technical effects in terms of spatial control capability and energy utilization efficiency.

[0036] To facilitate a deeper understanding of the technology in this invention, a detailed description of a multi-spectral phase-modulated bone and joint magnetic therapy system disclosed in the embodiments of this application is provided below. Please refer to [link to relevant documentation]. Figure 1 As shown, the system includes: The main control unit 100 is used to generate a multi-frequency stimulus sequence parameter set, which includes spectral partitioning parameters, phase progression parameters, and migration sequence parameters; its parameter generation process corresponds to a unique output result under the same input conditions. In implementation, regarding the division of frequency ranges, the preset frequency range is divided into a fixed number of continuous sub-ranges during system initialization. The upper and lower boundaries of each sub-range are pre-stored in memory as an array and do not change during operation. The reference frequency value of each sub-range is directly taken as the median of the corresponding upper and lower boundaries to avoid inconsistencies in results caused by different value selection methods.

[0037] The period length is calculated by the reciprocal of the reference frequency. During the sorting process, only the period length is used as the sorting criterion; no other weighting parameters are introduced. The sorted result forms a unique ordered sequence, and all subsequent parameter calculations are based on this sequence without re-sorting.

[0038] The difference between adjacent periods is calculated item by item according to the index order of the ordered sequence. During normalization, the maximum period difference is used as the divisor. In addition, when the maximum period difference is zero, the normalization step is skipped and all normalization results are set to zero, thereby avoiding division by zero.

[0039] In the calculation of the phase progression parameter, the slope and intercept of the linear function are written into the storage unit as fixed parameters during system initialization. Each normalized difference is directly substituted into the function to calculate the corresponding phase progression angle without interval selection or manual adjustment.

[0040] During the migration sequence generation process, the starting time of the time window for the first frequency interval is fixed at zero. The starting time of each subsequent time window is obtained by summing the starting time of the previous time window and its length; there is no independent assignment process. The time window length is obtained by multiplying the normalized difference by a fixed scaling factor, which is a preset constant.

[0041] To ensure that there is no overlap between time windows, when generating each time window, its start time is compared with the end time of the previous time window. If the two are inconsistent, the end time of the previous time window is used as the start time of the current window for correction, thereby forming a continuous and seamless time series.

[0042] Through the above processing method, the multi-frequency stimulus sequence parameter set generated by the main control unit 100 maintains consistency in the calculation path, avoiding differences in results caused by different parameter selections or calculation orders.

[0043] Next, please refer to Figure 4The diagram shows a system structure for spectrum partitioning and phase recursion expansion based on period difference hierarchical control. A multi-frequency stimulus sequence is used as input data and processed by the spectrum construction unit 200. This unit first performs periodic mapping on the input frequency components and forms a difference distribution feature based on the period difference corresponding to each frequency component. Based on this feature, the frequency components are grouped to obtain multiple spectrum region structures. A reference frequency component is selected within each spectrum region, and its corresponding initial phase is used as a reference phase. Simultaneously, a time interval structure corresponding to each spectrum region is established by combining a unified time reference, creating a one-to-one correspondence between the frequency structure and the time structure. The spectrum region structure, reference phase, and time interval structure output by the spectrum construction unit 200 are input as constraints to the phase expansion unit 300.

[0044] The phase expansion unit 300 starts with the reference phase of each spectral region, determines the phase increment based on the period difference classification result in the period dimension, and performs period-by-period accumulation processing on the reference phase to form a phase sequence that varies with the period. In this process, the phase sequence is kept within a preset phase interval by limiting the range of phase values.

[0045] Furthermore, the phase sequence is mapped to the time domain. By establishing a proportional relationship between the phase values ​​and the corresponding period parameters, the phase offset is converted into a time offset, and discrete positioning is performed within the time interval structure based on the time offset. Each frequency component corresponds to a specific time unit position on the time axis and forms an ordered distribution according to the time index.

[0046] The time units corresponding to different frequency spectrum regions are organized under a unified time reference, so that each frequency spectrum region forms a continuous but distinct distribution relationship in the time dimension, thereby completing the overall transformation process from frequency structure to phase structure and then to time structure.

[0047] Specifically, the spectrum construction unit 200 divides the multi-frequency stimulus sequence into frequency intervals based on the spectrum partitioning parameters, forming at least two independent spectrum regions, and establishes a corresponding frequency reference phase for each spectrum region. This unit includes a frequency analysis subunit, a period mapping subunit, an interval partitioning subunit, and a reference phase generation subunit. Note that the spectrum construction unit 200 does not simply group the multi-frequency signal, but constructs a discrete spectrum structure around the period difference distribution. Its core is to establish a stable partitioning relationship between frequency components through the period difference value.

[0048] The multi-frequency stimulus sequence is input as a discrete frequency array, for example, denoted as The frequency analysis process does not involve spectrum estimation; it only extracts frequency components according to a predetermined order of the input sequence, thereby avoiding uncertainty introduced by the transformation algorithm.

[0049] During the periodic mapping process, each frequency corresponds to a period. The reference frequency is not selected by external setting, but directly takes the value corresponding to the minimum frequency, and the corresponding reference period is... The period difference is calculated using a unified expression: The calculation order is consistent with the original index, without introducing a reordering step, thus avoiding multi-path results.

[0050] The partitioning of the period difference is not arbitrary, but rather uses a fixed-boundary discretization method. Let the range of the period difference be... Divide it into equal parts There are several intervals, among which This is a preset constant. Each frequency component is assigned to its corresponding interval according to the following rules: in Frequency components within the same interval constitute a spectrum region, and this division process does not involve dynamic threshold adjustment.

[0051] The reference phase is established using the frequency corresponding to the minimum period difference within the interval as the anchor point, rather than being arbitrarily selected. Let a certain frequency range be... Then its reference frequency satisfies: Its corresponding initial phase It directly inherits the original phase value of that frequency from the input sequence.

[0052] The phase shift of other frequency components within the same frequency range is not determined by looking up tables or empirical settings, but rather by the proportional relationship of period differences. The relative phase is calculated as follows: in This is a preset scaling factor, which is written during system initialization and is not adjusted during runtime.

[0053] For the unified processing of the time base, instead of directly selecting a specific frequency period, an integer extension of the maximum period is used. The unified time base period satisfies: in Let be the smallest positive integer such that all An integer ratio approximation is formed within this period. This process ensures that each spectral region can be aligned on a uniform time scale.

[0054] The time occupancy length of each spectrum region is normalized and allocated according to its reference frequency period: in This represents the period corresponding to the reference frequency of the spectrum region. The time intervals are linearly expanded according to the spectrum region index order, with the starting point of the first interval fixed at zero, and the remaining intervals satisfying a recursive relationship. During the interval splicing process, overlap is not checked separately; instead, the recursive structure described above naturally ensures interval continuity. If minor deviations occur due to rounding errors, compensation is uniformly applied to the last interval to ensure the total duration is strictly equal to the specified value. .

[0055] The switching position between spectrum regions is not triggered by external conditions, but is directly defined as the boundary point between adjacent time intervals, i.e. This point serves as both the end of the previous interval and the beginning of the next interval.

[0056] In practice, the spectrum construction unit 200 forms a unified computational constraint at three levels: frequency grouping, phase establishment, and time interval construction. This ensures that the spectrum division results, reference phase relationships, and time distribution structure are all uniquely determined by the same set of periodic parameters, without relying on runtime adjustments or external intervention.

[0057] The phase expansion unit 300 is used to perform progressive phase shift processing on the frequency reference phase of each spectral region according to the phase progression parameter within a continuous stimulation period, generating a phase progression sequence so that each spectral region forms a gradually changing phase structure in a continuous period; its processing is unfolded around the discrete distribution of the period difference, rather than performing phase modulation independently.

[0058] For the frequency components within each spectral region, the period difference This was determined before entering this unit. In this unit, the differences are not recalculated; instead, existing differences are directly processed through segmented mapping. Specifically, the periodic difference intervals are... The spectrum is divided into several discrete intervals according to fixed boundaries, and the numbering of each interval is kept consistent with that in the spectrum construction stage to avoid duplicate partitioning.

[0059] The phase step size is not set independently, but is directly determined by the difference interval number. In a specific implementation, the phase step size corresponding to each interval is generated in a linearly increasing relationship, for example, the... The step size corresponding to each interval is: in For a fixed increment, This is the minimum step size value. This relationship is determined during system initialization and remains unchanged during operation. Therefore, the phase step size of each frequency component is uniquely determined only by its corresponding interval.

[0060] Phase progression employs a cycle-by-cycle accumulation method, but the accumulation process maintains a single update path. Suppose a certain frequency component is at the [missing information - likely a specific frequency value]. The phase of each cycle is Then we have: in A preset phase period range is defined. In implementation, the modulo operation is performed at the end of each period to ensure that all phase values ​​always fall within a uniform range.

[0061] It should be noted that the phase updates of each frequency component are not reset synchronously, but are kept in an accumulated state in the continuous period. That is, there is no unified zeroing operation at the boundary of the period, thus ensuring the continuity of the phase structure in the time dimension.

[0062] In the phase-to-time domain conversion process, continuous-time representation is not used directly; instead, discrete-time units are introduced as intermediate mapping carriers. Each period is divided into a fixed number of time units, for example, divided into... There are 1 unit of equal length, and the length of each unit is... .

[0063] A proportional mapping relationship is used between the phase value and the time offset: The time offset is determined by comparing it with the length of the time unit, specifically by taking the integer index value of the interval in which it belongs, without interpolation.

[0064] Within the same period, all frequency components are sorted according to their time unit index. The sorting rule is that the index value is from smallest to largest, and if the indices are the same, they are arranged in the original frequency order, thus avoiding sorting ambiguity.

[0065] A time-activated sequence at the spectrum region level consists of a set of time units for all frequency components within it. During the generation process, individual frequencies are not scheduled independently; instead, time units within the same spectrum region are merged to form continuous or discrete activation segments.

[0066] The time relationship between different spectrum regions is not readjusted within the unit, but the interval structure determined by the spectrum construction unit 200 is maintained. The phase-to-time expansion is only completed within the interval, thereby ensuring that the responsibility boundaries between each unit are clear.

[0067] The migration scheduling unit 400 is used to temporally reconstruct the phase progression sequence according to the migration sequence parameters, establish the sequential activation relationship of the spectral regions in continuous stimulation cycles, and form a spectral migration sequence unfolded along the time axis; its processing object is the discrete time unit sequence output by the phase unfolding unit 300. Each spectral region corresponds to a set of discrete time unit indices in each cycle, and the index represents the position in a unified time base period in integer form. To avoid multiple scattered activations in the same spectral region within a cycle, resulting in a non-unique center position, the time unit indices of the spectral region are first deduplicated and sorted in ascending order to form an ordered index set.

[0068] The calculation of the center activation time does not employ the geometric center or interval midpoint method, but instead directly uses a weighted average based on the index values. Let the set of time unit indices corresponding to a certain spectral region be . The activation time of the center is determined as follows: ,in The duration of a single time unit is determined during system initialization by a unified time base period and the total number of time units. The above calculation does not introduce weight adjustments, thus avoiding artificial bias.

[0069] The calculation of scheduling priority parameters strictly follows a preset formula, where all variables are derived from the determined output of the preceding unit. Among these, a unified time base period is used. For fixed values, periodic difference The calculation results are directly inherited from spectrum building unit 200 and will not be recalculated in this unit. Number of frequency components. The weighting coefficients are obtained by counting the frequency set within the specified frequency range. Write to memory during system initialization and satisfy normalization constraints. Dynamic adjustments are not allowed during operation. Therefore, the scheduling priority parameter... It has a unique calculation result under the same input conditions.

[0070] During the sorting implementation, for all spectral regions The values ​​are compared numerically and arranged in ascending order. When two corresponding spectral regions appear... When the values ​​are equal, random selection is not introduced, but fixed rules are used for resolution, that is, the spectral region with the smaller center activation time is selected first; if they are still the same, they are arranged according to the original numbering order of the spectral regions in the spectrum construction stage, so as to ensure that the sorting result is unique.

[0071] Cross-cycle continuity constraints are not achieved by recalculating priorities, but rather by adjusting positions based on the already determined sorting results. Specifically, the current cycle sorting result is treated as a circular sequence, and the end time of a certain spectral region in the previous cycle is denoted as... In the current cycle, select from the sorted sequence a timer whose starting activation time is the same as the starting activation time of the current timer. The spectral region with the smallest difference is used as the starting point, and the remaining spectral regions are expanded cyclically according to their original sorting order. This process only involves the cyclic shifting of the sequence and does not change the internal relative order.

[0072] To avoid time overlaps or gaps at the transition between cycles, after performing cyclic shift, the start time of the first spectrum region is checked for consistency with the end time of the previous cycle. If there is a deviation, the entire spectrum region is shifted backward by the corresponding difference, while the remaining spectrum regions maintain their relative intervals, thus forming a continuous time series.

[0073] During implementation, the migration scheduling unit 400 does not directly allocate time to the spectrum region. Instead, it first defines constraints on the basic parameters involved in the calculation to avoid different implementation paths leading to non-unique results. (Period difference) Using the period corresponding to the same reference frequency The difference form, i.e. ,in A period value corresponding to the representative frequency is selected for the i-th frequency region. To ensure consistency in parameter selection within the same frequency region, when multiple frequency components exist, the period corresponding to the median frequency is preferably chosen as the period value. Alternatively, in the implementation, the period corresponding to the minimum frequency in the frequency spectrum region can be fixed to ensure that the parameter does not jump in different operation periods.

[0074] The standardized periodic parameters It is not the original period, but the result after dimensionless processing, and its calculation form is limited to: This ensures that all variables involved in the weight calculation are within the same scale, avoiding the unintended amplification effect of different frequency orders of magnitude on the exponentiation result. In hardware implementation, this process is achieved through fixed-point normalization or table lookup to guarantee computational efficiency and numerical stability.

[0075] During the weight calculation stage, the nonlinear coupling is not an arbitrary combination, but is limited to a power function form, the expression of which is: Where the exponential coefficient The control unit writes the values ​​to the registers during system initialization, and these values ​​do not dynamically change with each single stimulus, ensuring that the weight allocation result is uniquely determined under the same input conditions. This is to avoid situations where... Weight degradation or numerical instability may occur during implementation. Set lower threshold That is, when At that time, uniformly according to Involves in calculations to avoid concentrating weights in a single frequency range.

[0076] Obtaining weights Subsequently, it is not directly used for continuous-time calculations, but rather mapped to a discrete-time structure. Specifically, a unified time reference period is established. The system is divided into a fixed number of discrete-time units. The length of each time unit is ,in For example, the value is a preset integer. to The time window length for each spectral region is determined to balance temporal resolution and processing overhead. in This represents the rounding operation. Because the rounding process may result in... After the calculation is completed, the system performs an error compensation step, which distributes the difference to the spectrum region with the largest weight according to the weight size rule or distributes it in a sequential cycle to ensure that all time units are fully occupied and there are no gaps or overflows.

[0077] During the time window arrangement process, a recursive generation method is used to determine the start and end positions of each window. Specifically, the starting point of the time window for the first spectral region is fixed at time index 0, and its ending point is... The starting point of the i-th spectral region is equal to the ending point of the (i-1)-th window plus 1, and its ending point is the starting point plus 1. The time series constructed in this way is structurally guaranteed to be strictly continuous, with no overlapping or unassigned intervals. The time series is recorded in the storage structure as a sequential array, with each item containing a spectral region identifier and its corresponding time length, used as boundary constraints in subsequent migration path calculations.

[0078] It should be further clarified that the time window allocation result in this system does not directly correspond to the current output segment, but rather serves as an "occupancy framework" for migration scheduling. When constructing continuous migrations between adjacent frequency regions, the actual activation state will smoothly transition at the boundary between two adjacent windows, as mentioned above... Only the dominant interval length of each spectral region within the overall cycle is limited. This approach allows for the introduction of local continuous variations while maintaining overall time structure stability, thus avoiding the current surges caused by hard switching in traditional segmented control.

[0079] The transition time interval is not generated outside the unified time base period, but is reconstructed from within the predetermined time windows of two adjacent spectrum regions. Specifically, at the end of the time window of spectrum region i and at the beginning of the time window of spectrum region i+1, a portion of time is reserved for constructing the transition interval, and the total length of this portion of time satisfies the following condition: The proportionality coefficient mentioned above The transition interval is set during system initialization and stored in the control register. Its value is preferably between 0.1 and 0.5 to avoid abrupt changes due to an excessively short transition interval, or compression of the dominant region due to an excessively long one. The specific location of the transition interval on the time axis is determined as follows: its start time... Defined as the end of the time window of spectrum region i minus The termination time is the spectrum region Add the start of the time window This ensures that the length of the entire time axis remains constant and that no additional intervals are inserted.

[0080] Within the transition interval, a continuous weighting function is introduced to describe the occupancy relationship between the two spectral regions, and its expression is: The exponent parameter p is used to adjust the degree of non-linearity of the transition. In engineering implementation, this parameter is usually taken to a value between 1 and 3, and the exponentiation is implemented by looking up a table to reduce the computational burden on the embedded processor. It should be noted that the above weighting function is only used to describe the continuous change trend and is not directly used as the control signal to drive the two frequency regions in parallel.

[0081] Since this system requires that only one spectrum region be active at any given time in the execution layer, a discrete decision mechanism is introduced in the transition region to map continuous weights to a single activation assignment. Specifically, the transition region is divided into discrete time units n, and the corresponding value for each time unit is calculated. and Then, based on the comparison results, the affiliation of that time unit is determined, that is, when If the time unit is determined to belong to spectrum region i, it is otherwise determined to belong to spectrum region i+1. In this way, continuous weight changes are achieved macroscopically, while maintaining activation of a single spectrum region microscopically, thereby avoiding the current superposition problem caused by simultaneous driving of multiple frequencies.

[0082] Furthermore, to avoid high-frequency switching near the weight crossover point, a minimum duration constraint is introduced into the decision-making process in the actual implementation. This means that once the same spectrum region is activated, it must remain active for at least a certain number of time units before switching can occur. This duration threshold is set according to the system sampling frequency, for example, 2 to 5 time steps, to suppress jitter. This constraint is implemented by adding a state latch flag to the scheduling queue, without changing the overall weight distribution trend.

[0083] After making the above decision, the migration scheduling unit 400 reconstructs the original time activation sequence. That is, within the time index range corresponding to the transition region, the decision result replaces the original single spectral region identifier, thereby generating a new time sequence. This sequence corresponds to only one spectral region identifier at any given time and can be directly used as the input for subsequent current parameter mapping. Through the above processing, the activation boundary of the spectral region is no longer abrupt, but forms a gradually advancing switching process on a discrete time scale, presenting as a continuous migration stimulus path as a whole.

[0084] It is important to note that the aforementioned transition zone construction and weight adjustment do not change the total occupancy ratio of each spectral region within the complete time reference period; they only partially rearrange their distribution along the time axis, thus maintaining consistency with the time window length calculated based on the weights in the previous weighting. This approach introduces a local continuous change mechanism without disrupting the global scheduling structure, thereby reducing the rate of current change when driving the magnetic stimulation coil and improving the smoothness and controllability of the output waveform. This implementation differs from simple boundary smoothing or filtering in existing technologies; its core lies in explicitly constructing a migration structure within the time domain to achieve a controllable transfer of the spectral dominance relationship.

[0085] The magnetic drive unit 500 is used to generate a corresponding pulse drive current sequence based on the spectrum transfer sequence and apply it to the magnetic stimulation coil. In specific implementation, the spectrum transfer sequence is stored in the system in the form of a time index array, where each time unit corresponds to a unique spectrum region identifier and its time occupancy weight at that moment. This weight is 1 in the non-transition region, and is calculated by the preceding unit and changes monotonically with time in the transition region. After reading the sequence, the magnetic drive unit 500 processes it in a fixed time step. As a scheduling cycle, a set of pulse drive parameters is generated within each time step.

[0086] The current amplitude The calculation is not directly output using floating-point arithmetic results, but is implemented in the embedded controller through a combination of table lookup and fixed-point arithmetic. Specifically, the standardized periodic parameter... During system initialization, normalization was completed and the data was stored as a fixed-point value, including the reference current amplitude. Based on the rated current of the magnetic stimulation coil and the capability of the driving circuit, the value is preset, for example, ranging from 0.5A to 5A. The exponential coefficients a and b are stored in discrete increments, and the result of the exponentiation is obtained by looking up a table, thus calculating: To avoid drive failure due to excessively low current amplitude when the transition region weight is small, the implementation includes... Set lower threshold When the calculation result is lower than this threshold, it is processed according to... Output to ensure the coil is always in a controllable working state.

[0087] The pulse width With pulse interval It is constrained by both the length of the current time unit and the period of the corresponding frequency spectrum region. In implementation, it is first determined based on the original period corresponding to the frequency spectrum region. Calculate the number of pulses that should be output within this time unit. ,when At that time, a cross-time-unit accumulation method is used to complete a full cycle output within multiple time units. Subsequently, pulses are distributed at equal intervals within that time unit, with the pulse intervals satisfying... Pulse width Then, based on the duty cycle coefficient, it is set as follows: ,in The preset ratio is preferably between 0.1 and 0.5 to avoid coil overheating or driver saturation.

[0088] To suppress sudden current changes caused by spectrum switching or weight changes between adjacent time units, the magnetic drive unit 500 sets a current change rate constraint. This constraint is implemented through amplitude limiting filtering, i.e., limiting the calculated target current... Compared with the actual output current at the previous moment A comparison is made, and when the difference between the two exceeds a threshold... At that time, the output current is only allowed to be updated according to the maximum change step size, that is: Otherwise, directly order The above processing is achieved in the digital controller through simple addition and subtraction operations, without introducing additional delay. Threshold The value is set according to the response capability of the drive circuit and the inductance characteristics of the coil, for example, the current change per time step should not exceed 5% to 10% of the rated current.

[0089] In practice, the pulsed drive current is applied to the magnetic stimulation coil through a power drive circuit. The drive circuit preferably employs a switching structure composed of MOSFETs or IGBTs, with the microcontroller outputting PWM or timing pulse signals to control its on / off state. The current amplitude is achieved by adjusting the supply voltage or duty cycle, while the pulse width and interval are precisely controlled by a timer module. To ensure that the output current matches the calculated value, a current sampling resistor or Hall sensor is incorporated into the circuit for real-time feedback, and the drive signal is fine-tuned through closed-loop control to compensate for the effects of power supply fluctuations or load changes.

[0090] Through the above processing, the discrete-time structure in the spectrum shift sequence is gradually transformed into a current output waveform with continuously varying characteristics. On the time scale, this manifests as a smooth shift in the relationship between stimulus intensity and frequency dominance, while maintaining the pulse-driven form corresponding to a single spectrum at any given microscopic moment. This implementation avoids the current interference problem caused by the direct superposition of multi-frequency signals, and simultaneously ensures the stability of the driving process through rate-of-change constraints, enabling the entire system to form a closed-loop, consistent execution path from the scheduling structure to the physical output.

[0091] Finally, it should be noted that the mathematical formulas, derivations, symbol definitions, and parameter calculation methods used in this specification are all for the purpose of further clarifying and verifying the technical content of this invention, so that those skilled in the art can more intuitively and accurately understand the working mechanism and technical effects of this invention. These formulas are only used as quantitative expressions or illustrative examples of technical features and do not constitute limiting conditions of the claims of this invention. Those skilled in the art should understand that, without changing the core idea of ​​this invention, the parameter forms, calculation methods, numerical ranges, and even symbol representations involved in the formulas can be equivalently replaced or simplified in engineering according to the actual application environment. The specifics can be determined according to the actual situation, and no limitation is imposed. It should also be emphasized that the formulas in this specification are not theoretical derivations in the style of academic research papers, but rather an engineering description of the embodiments of this invention. Their purpose is to enhance the understandability and implementability of this invention, rather than to increase redundancy and complexity. Those skilled in the art can choose whether to use such quantitative tools when reading this specification, or can achieve the same technical effects through other equivalent methods.

[0092] Furthermore, while specific embodiments of the present invention have been described above, those skilled in the art should understand that these specific embodiments are merely illustrative. Those skilled in the art can omit, substitute, and modify the details of the above methods and systems in various ways without departing from the principles and essence of the present invention. For example, combining the above method steps to perform substantially the same function and achieve substantially the same result according to substantially the same method falls within the scope of the present invention. Therefore, the scope of the present invention is defined only by the appended claims.

Claims

1. A multi-spectral phase-modulated bone and joint magnetic therapy system; characterized in that: The system includes a main control unit, a spectrum construction unit, a phase unfolding unit, a migration scheduling unit, a magnetic drive unit, and a magnetic stimulation probe; The main control unit is used to generate a multi-frequency stimulation sequence parameter set, which includes spectral partitioning parameters, phase progression parameters, and migration sequence parameters. The spectrum construction unit is used to divide the multi-frequency stimulus sequence into frequency intervals based on the spectrum partitioning parameters, forming at least two independent spectrum regions, and establishing a corresponding frequency reference phase for each spectrum region. The phase unrolling unit is used to perform progressive phase shifting processing on the frequency reference phase of each spectral region according to the phase advancement parameter within a continuous stimulation cycle, generating a phase advancement sequence so that each spectral region forms a gradually changing phase structure in a continuous cycle. The migration scheduling unit is used to perform temporal reconstruction of the phase progression sequence according to the migration sequence parameters, establish the sequential activation relationship of the spectral region in the continuous stimulation cycle, and form a spectral migration sequence unfolding along the time axis. The magnetic drive unit is used to generate a corresponding pulse drive current sequence according to the spectrum migration sequence and apply it to the magnetic stimulation coil; The magnetic stimulation probe is electrically connected to the magnetic drive unit. The magnetic stimulation probe contains a magnetic stimulation coil. Under the action of the pulse drive current sequence, the magnetic stimulation coil outputs a corresponding temporal magnetic field structure. The temporal magnetic field structure forms a magnetic stimulation field distribution in the human bone and joint region that unfolds according to the spectral migration sequence.

2. The multi-spectral phase-modulated bone and joint magnetic therapy system according to claim 1, characterized in that: The process of generating the multi-frequency stimulus sequence parameter set includes: The preset frequency range is divided into multiple continuous frequency intervals, and the center frequency of each frequency interval is taken as the reference frequency value. Calculate the corresponding period length based on each reference frequency value, and sort each frequency interval in descending order of period length to obtain the spectrum partition parameters; Calculate the period difference between adjacent frequency intervals after sorting, and normalize each period difference based on the maximum period difference to obtain a normalized difference sequence. Based on the normalized difference sequence, the phase advance angle value between each adjacent frequency interval is calculated according to a preset linear function relationship to generate phase advance parameters; The first frequency interval in the ordered frequency sequence is taken as the starting interval. Time windows are assigned to each frequency interval in the order of the ordered frequency sequence. The length of the time window for each frequency interval is calculated by the corresponding normalized difference through a preset scaling factor, forming a continuous and non-overlapping migration sequence parameter.

3. The multi-spectral phase-modulated joint magnetic therapy system according to claim 1, characterized in that: The spectrum construction unit includes a frequency analysis subunit, a period mapping subunit, an interval division subunit, and a reference phase generation subunit. The frequency analysis subunit is used to extract each frequency component in the multi-frequency stimulus sequence and form a frequency set. The period mapping subunit is used to perform period calculation on each frequency component in the frequency set to obtain a corresponding period parameter set, and calculate the period difference of each period parameter relative to the reference period with the period corresponding to the preset reference frequency as a reference. The interval division subunit is used to sort the frequency set based on the period difference and divide it according to the hierarchical interval of the period difference, so that each frequency component in the same spectrum region satisfies that the period difference is within the same difference interval, forming multiple spectrum regions; the reference phase generation subunit is used to select a reference frequency component for each spectrum region, and use the initial phase of the reference frequency component as the reference phase of the spectrum region, and at the same time establish the phase mapping relationship between the frequency component and the reference phase according to the period difference of each frequency component in the spectrum region relative to the reference frequency component.

4. The multi-spectral phase-modulated bone and joint magnetic therapy system according to claim 3, characterized in that: The spectrum construction unit also includes: The time base generation subunit is used to determine the unified time base period based on the period parameter set, and to map the period of the reference frequency component in each spectrum region to the unified time base period to obtain the standardized period parameters corresponding to each spectrum region. The interval constraint subunit is used to calculate the time occupancy length of each spectrum region within the unified time reference period based on the standardized period parameters of each spectrum region, and to allocate time intervals to each spectrum region according to the time occupancy length, so that only one spectrum region is in the active interval at any given time. At the same time, the switching boundary between adjacent spectrum regions is determined by the difference in their standardized period parameters, forming multiple non-overlapping spectrum interval sequences on the time axis.

5. The multi-spectral phase-modulated joint magnetic therapy system according to claim 1, characterized in that: The operation of the phase unrolling unit includes: The period difference corresponding to the frequency component in each frequency region is processed in a hierarchical manner, the period difference is mapped to a preset difference interval, and a corresponding phase step value is assigned to each difference interval to form a phase step set. Using the reference phase of each spectral region as the initial phase, the frequency components are iteratively calculated cycle by cycle within a continuous stimulation period. The phase value in the nth cycle is obtained by adding the phase value of the (n-1)th cycle to the corresponding phase increment value. After each cycle calculation, a period modulo operation is performed on the obtained phase value to limit the phase value within a preset phase range, and the phase sequence corresponding to each frequency component in each cycle is obtained.

6. The multi-spectral phase-modulated joint magnetic therapy system according to claim 5, characterized in that: The phase expansion unit is also used to convert the phase sequence corresponding to each frequency component in each period into a time sequence, the process of which includes: Based on the period parameters corresponding to each frequency component, the phase values ​​in the phase sequence are proportionally converted into time offsets relative to the start time of the current period. The time offset is equal to the product of the phase value and the corresponding period divided by a preset phase period range. Each cycle is divided into multiple consecutive time units, and the time unit index corresponding to each frequency component is determined according to the time offset, so that each phase value corresponds to a unique time unit position. The frequency components are sorted by time unit index, and time units belonging to the same spectrum region are aggregated to generate the time activation sequence corresponding to each spectrum region in a continuous period.

7. The multi-spectral phase-modulated joint magnetic therapy system according to claim 1, characterized in that: The working process of the migration scheduling unit includes: Based on the time activation sequence corresponding to each spectrum region, the time unit index set of each spectrum region in each period is extracted, and the center activation time of each spectrum region in the current period is calculated. The center activation time is the weighted average of the corresponding time unit index. Scheduling priority parameters are constructed for each spectrum region. These parameters are obtained by coupling the center activation time, standardized period parameters, and period difference of each spectrum region. The calculation formula is as follows: in, Indicates the first Scheduling priority parameters for each spectrum region; Indicates the first The central activation time of each spectrum region; Indicates a unified time base period; Indicates the first The period difference of each frequency region relative to the reference frequency component; Indicates the first The number of frequency components contained in each spectrum region; The preset weighting coefficients are used, and they satisfy the following conditions: ; The spectrum regions are sorted according to the scheduling priority parameters, and the activation order of the spectrum regions in the current period is generated based on the sorting results. Between adjacent cycles, the activation order of the spectrum region is subjected to continuity constraint processing, so that the activation start position of the spectrum region in the later cycle and the activation end position of the spectrum region in the previous cycle maintain the minimum time interval, forming a continuous spectrum migration sequence across cycles.

8. The multi-spectral phase-modulated joint magnetic therapy system according to claim 7, characterized in that: The migration scheduling unit is also used to allocate time windows corresponding to the activation order of each spectrum region. The working process includes: Extract the period difference and standardized period parameter corresponding to each spectral region, and perform nonlinear coupling calculations to construct a time window allocation weight parameter. The calculation formula is as follows: in, Indicates the first Weighting is assigned to each spectrum region within a time window. Indicates the first The period difference of each frequency region relative to the reference frequency component; Indicates the first Standardized periodic parameters for each spectrum region; To preset nonlinear exponential coefficients, and ; Indicates the total number of spectrum regions; Based on the weighting parameters assigned within the time window, a unified time base period will be established. The frequency spectrum is divided into multiple consecutive time windows, with the length of each time window corresponding to a specific frequency region. ; The time windows are arranged sequentially according to the activation order of the spectrum regions, so that each spectrum region occupies the corresponding time window in sequence within a unified time base period, and any two adjacent time windows are connected end to end without overlap, forming a complete time occupancy structure sequence.

9. A multi-spectral phase-modulated bone and joint magnetic therapy system according to claim 8, characterized in that: The migration scheduling unit is also used to construct a continuous transition interval between time windows of adjacent spectrum regions, and the working process includes: In two adjacent spectral regions arranged in the activation order and At the boundary of the time window, the transition time interval is divided according to the length of the time window of the corresponding two frequency regions. The formula expression is: in, Indicates the spectrum region With the spectrum region The length of the transition time interval between them; Representing the spectrum regions and Time window length; This is a preset proportional coefficient, and ; During the transition time interval, for the spectrum region With the spectrum region The time occupancy weight is continuously adjusted, and the frequency spectrum is adjusted through a weight change function. The occupancy weight is gradually reduced from 1 to 0, while the spectrum region is... The weight of the occupancy gradually increases from 0 to 1, and the formula is as follows: in, They represent the times respectively. At that time, the spectrum region With the spectrum region Time occupancy weight; Indicates the start time of the transition time interval; It is a non-linear adjustment index, and ; Within the transition time interval, the time activation sequence of the corresponding spectrum region is reconstructed according to the time occupancy weight, so that only one spectrum region is active at any given time, and the activation attribution of the spectrum region is switched according to the magnitude of the time occupancy weight, thus forming a spectrum migration path within the continuous stimulation cycle.

10. A multi-spectral phase-modulated bone and joint magnetic therapy system according to claim 1, characterized in that: The operation process of the magnetic drive unit includes: Based on the spectral region identifiers corresponding to each time unit in the spectral migration sequence, a mapping relationship between time units and driving current parameters is established, and a corresponding pulse driving current parameter set is generated for each time unit. The pulse driving current parameter set includes current amplitude. Pulse width and pulse interval ; Wherein, the current amplitude The calculation is performed by coupling the standardized periodic parameters and time occupancy weights of the corresponding spectrum region. The calculation formula is as follows: in, Indicates time The magnitude of the driving current; Indicates the preset reference current amplitude; The standardized periodic parameter represents the frequency range to which the current time unit belongs; Indicates a unified time base period; Indicates the corresponding spectral region at time Time occupancy weight; For the preset exponential coefficient, and ; The pulse width With pulse interval The calculation is performed in segments based on the length of the time unit and the period parameter of the corresponding spectrum region. The number of pulses in each time unit satisfies the output frequency that is consistent with the period of the spectrum region. Between adjacent time units, the current amplitude Continuity constraints are applied to ensure that the rate of change of current between adjacent time points does not exceed a preset threshold. ,satisfy ,in, Indicates the interval between adjacent time units; Based on the set of pulse drive current parameters, the magnetic stimulation coil is switched on and off by the drive control circuit, and the pulse drive current is output sequentially in a time sequence.

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