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Comparison of Current Device with First Generation Device
The first generation device is the Jacobson Resonator™, the current or next generation device is referred to as the Resonator™ device and is described “above”. The current device was developed to address the following issues and shortcomings with the first generation device (ie the Jacobson Resonator™).
Both the current and the old electromagnetic therapy systems produce low-level magnetic fields in the micro-Tesla range and below, over frequencies of a few hundred Hertz down to DC. The magnetic fields of the predecessor system are generated using magnetic coils that are driven by low-current levels (e.g., micro-amperes and lower) created by magnetic therapy drivers which include an off-the-shelf signal generator in series with a manual attenuator (i.e., a manual switch-box containing discrete resistors). The magnetic coil used may be a Helmholtz coil, which produces an especially uniform field, although many other coil configurations are possible (e.g., a solenoid, a poloidal coil, a toroid, etc.). However, in practice, the use of a manual attenuator is problematic in that manual attenuators are imprecise and inaccurate for use in low-level magnetic therapy drivers, resulting in magnetic fields that may deviate significantly from desired operation, and may vary from unit to unit. In addition, for normal operation, manual calibration of the attenuator is required for every coil that is used with it. Consequently, whenever a coil is changed to alter a magnetic therapy treatment, recalibration is necessary. This approach is time consuming, cumbersome and prone to operator error. As a result, a need exists for a more precise magnetic therapy driver that can be used with alternative sets of coils, without the need for recalibration.
In addition to the foregoing, manual attenuators are also problematic in that the discrete resistors they use are a well-known and significant source of electrical noise (e.g., 1/f noise, and shot noise). As a result, a resistive attenuator will introduce additional error into the magnetic field delivered by the magnetic therapy driver. Therefore what was also needed was a low-noise magnetic therapy driver.
Furthermore, the ability to create sequential and programmable time-sequences of different waveforms (e.g., sinusoidal or square wave) is also essential for many magnetic therapy applications. Presently, complex regimes of time-sequenced magnetic waveforms are accomplished by manual switching of the off-the-shelf signal generator and manual attenuator. This approach is inaccurate, cumbersome and prone to operator error. Consequently, a precise control of electronic signal waveforms that drive the magnetic coils is required. As a result, what is needed is a programmable magnetic therapy driver.
Several other improvements have also been incorporated for ease of use, and to produce a precise and accurate magnetic therapy driver, which may be readily appreciated by those skilled in the art. A need existed to minimize electronic errors due to non-linearity and stray AC and DC offsets in the magnetic therapy driver. A need existed for the magnetic therapy driver to be able to be located near the magnetic coils, thereby minimizing cable length to the coils, which is a source of electrical noise, and therefore, error. A need also existed for a magnetic therapy driver capable of adjusting its output in proportion to ambient temperature, such that changes in temperature will have a reduced effect on the precision and accuracy of the magnetic therapy.
Additionally, the new system creates a PC-based graphical user interface that is easier to follow than the earlier version system that utilizes an off-the-shelf “function signal generator” that may be confusing and or intimidate those who may be unfamiliar with its use and function.
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