referring now to the drawings , where like elements are designated by like reference numerals throughout , fig1 shows an apparatus 10 , more fully described below , for treating wounds with electromagnetic energy . apparatus 10 includes an electromagnetic energy generating unit 12 with multiple ports 13 , and multiple applicators 14 connected to unit 12 by coaxial cables 16 . a power source 18 , such as a battery pack , is provided for delivering a current input to unit 12 . while shown in fig1 as a remote unit , battery pack 18 can be incorporated as part of unit 12 . since the present invention has low power requirements , the power source can be one capable of providing an average power input of less than three watts . referring to the block diagram of fig2 unit 12 includes a generator 30 for producing a pulsed high frequency signal output 32 and at least one applicator 14 having output 32 as its input . generator 30 includes a pulse generator 34 and one or more amplifiers 36 having as their inputs a pulsed signal output 38 from the pulse generator 34 . the number of amplifiers 14 is preferably equal to the number of treatment ports , such that each applicator 14 has an input from a single amplifier 36 . treatment energy pulse controller 40 is connected to pulse generator 34 for automatically controlling characteristics of output 38 such as pulse rate and pulse width . output 38 is delivered to amplifiers 36 , each of which is individually responsive to signals 42 , 42 i , 42 ii generated by power level controller 44 . control signals 42 , 42 i , 42 ii from the power level controller 44 reflect feedback information 54 from the field strength detector positioned on each applicator 14 . one or more control circuits , including the forward and reflected power measuring circuits 46 , the treatment timer 48 and the treatment energy pulse controller 40 , detect abnormal conditions and disable operation when appropriate . the power level controller 44 is also responsive to control signals 50 generated by control circuitry in the power supply assembly 52 and control signals 56 received from one or more proximity detectors located on the applicators 14 . treatment timer 48 , which delivers activation signals 58 , 60 to the power level controller 44 and the treatment energy pulse controller 40 , respectively , for instituting the treatment process over a predetermined period of time , is also responsive to shut down signals 62 from the power level controller 44 for disabling the apparatus 10 when certain conditions are detected . the embodiment of the unit shown in fig1 and 2 has three treatment ports 13 for simultaneously and independently delivering different output signals 32 to three separate applicators 14 . it should be understood that the number of ports 13 , amplifiers 36 and measuring circuits 46 may be varied without departing from the scope of the present invention . the apparatus shown in fig2 operates as follows . signals 58 , 60 from treatment timer 48 enable the power level controller 44 and the treatment energy pulse controller 40 , respectively , thereby enabling the pulse generator 34 to produce pulsed signal output 38 . controller 44 automatically controls specific characteristics of the pulsed signal output 38 produced by generator 38 and received by amplifiers 36 , including pulse rate , pulse width and pulse power level . the pulsed signal output 38 is thus amplified in accordance with instructions received from the power level controller 44 , and specific outputs 32 are produced . each of the outputs 32 may be different , depending on the specific instructions delivered to each amplifier 36 by controller 44 . outputs 32 from each amplifier 36 are evaluated by forward and reflected power measuring circuits 46 and delivered to applicators 14 which , in turn , use the output to apply a treatment dosage of electromagnetic energy to the patient . the power level controller 44 individually instructs each amplifier 36 in accordance with specific information received from the field strength detectors located on the applicators 14 . as described in greater detail below , power level controller 44 , in conjunction with multiple control circuits , also provides for automatic disablement of the apparatus when treatment is complete , when treatment dosages are at unacceptable levels , or when inadequate power is being delivered to the apparatus . for multiple applicator embodiments , unit 12 may include a single controller 44 with multiple circuits , each dedicated to a single amplifier 36 , for controlling multiple applicators 14 , or multiple separate and distinct controllers 44 , each having a single circuit for controlling a single applicator 14 . fig3 is a block diagram of the pulse rate generator 34 and treatment energy pulse controller 40 shown in fig2 . generator 34 includes three major subcircuits . the first subcircuit is a pulse rate timer 64 for generating a controlled frequency of occurrence of the pulse envelope . timer 64 sets the period , or pulse rate , of treatment dosage . the output of timer 64 is sent to a second subcircuit , the pulse width timer 66 , which produces a single consistently shaped pulse envelope . the output of timer 66 is then used as an enable pulse for the gated high frequency rf oscillator 70 of the pulse generator 34 . oscillator 70 generates electrical signals reflecting the characteristics defined by the enabling pulse . the generated electrical signal output 38 is then delivered to amplifiers 36 which increase the size or amplitude of the signals in response to instructions received from the power level controller 44 . for specific wound treatments , it has been demonstrated that maximum effectiveness results when the rf pulse rate , rf pulse width , and peak rf power level of the enable pulse are set at specific values . for example , the ed 50 dose for optimum stimulation of human and other mammalian fibroblasts is about 15 mw / cm 2 average rf power , with an ed 99 of about 32 mw / cm 2 , while the ed 99 for epithelial cells is about 100 mw / cm 2 . these dosages are based upon pulse envelopes with an optimum pulse duration of about 32 microseconds and a repetition rate of about 1 , 000 pulses per second . for example , in one embodiment particularly effective in treating pressure ulcers , timer 64 is set at between about 1 , 200 - 1 , 500 pulses per second , and timer 66 is set at between about 16 - 20 microseconds , giving an output of between about 30 - 40 mw / cm 2 average power . in another effective embodiment , timer 64 is set at between about 900 - 1 , 200 pulses per second , and timer 66 is set at between about 30 - 45 microseconds , giving an output of between about 30 - 65 mw / cm 2 average power . in another effective embodiment , timer 64 is set at between about 600 - 1 , 000 pulses per second , and timer 66 is set at between about 32 - 60 microseconds , giving an output of between about 30 - 100 mw / cm 2 average power . other treatment profiles are possible and can be used without departing from the scope of the present invention . referring once again to fig3 automatic control of operating parameters ( e . g ., pulse rate , pulse width , rf power level , treatment time , etc .) is managed by a treatment energy pulse shaper and pulse repetition controller circuit 40 . circuit 40 includes a custom control logic circuit 72 having numerous treatment profiles preset therein . a treatment mode selector control 74 permits the operator to quickly select one of the stored profiles . pulse control circuit 76 receives the signal from circuit 72 reflecting the desired pulse rate for the selected profile and sets the pulse rate timer 64 accordingly . similarly , width control circuit 78 receives the signal from circuit 72 reflecting the desired pulse width for the selected profile and sets the pulse width timer 66 accordingly . further , an rf power level is selected by the control logic circuit 72 and an appropriate signal reflecting that selection is sent to the power level controller 44 , shown in fig2 and 5 . the ability to easily select and automatically control operating parameters ( e . g ., pulse rate , pulse width , and rf power level ) is a very important feature lacking in previous devices . by employing a control logic circuit 72 , a plurality of treatment rf pulse profiles ( combination of specific rf pulse rates , rf pulse widths , and rf power level ) can be easily preset during assembly and manufacture . treatment mode selector control 74 is included to allow the operator to easily select the appropriate treatment profile . in one embodiment , control 74 is a rotory selector witch . preferably , the positions are clearly labelled as to their function . in another embodiment , control 74 is a touch pad or series of depressible buttons or keys for electronically or otherwise inputting a selection . it is understood that any means for selecting one or more of a number of stored profiles is contemplated by the present invention . in preferred embodiments , the only operator control besides control 74 is the start / stop button 80 ( fig4 ). in one embodiment of the present invention , the control logic circuit 72 is preset with a single treatment profile . in that embodiment , the actuating means ( e . g ., start / stop button 80 ) is all that is required to select and start treatment . where multiple applicators are used , the unit 12 is provided with multiple treatment selector controls 74 , one for each applicator 14 . it is possible , however , to combine those controls in a single structure ( e , g ., a touch pad ). fig4 is a block diagram of treatment timer 48 . to regulate the amount of time , or treatment dosage , that a patient is receiving the applied pulsed rf energy , a digitally controlled treatment timer 48 is provided . the treatment timer 48 is started by pressing an actuator 80 , such as a start / stop push - button , and is stopped by the operator by again pressing the actuator 80 . pressing actuator 80 sets digital latch 82 . setting the digital latch 82 starts several actions . first , a signal is sent to the treatment energy pulse controller 40 to enable its operation . second , a signal is sent to the power level controller 44 to enable its operation . third , setting the digital latch 82 enables a time base oscillator 84 . the output of oscillator 84 is sent to a multiple stage binary counter 86 , which at its last output stage , produces an extended square wave pulse after a fixed period of time . this square wave pulse is then sent to a timer control 88 , producing exclusive output signals . timer counter 88 is preset to a predetermined treatment time , automatically controlled by logic circuit 72 , or set by the operator using the treatment selector control 74 . when the timer control 88 counts down to a value of zero , an end of treatment output pulse is initiated and this pulse is then used to reset the digital latch 82 , disable the time base oscillator 84 , and disable the control logic circuit 72 . while the timer control 88 counts down , it is simultaneously sending signals which drive and correctly illuminate a treatment time display panel 90 . the treatment timer 48 can also be stopped by a disable pulse received from the power level controller circuit 44 . the disable signal is automatically generated when an operating deviation in the rf output circuitry is detected . fig5 is a block diagram of a power level controller 44 for incorporation in the present invention . the power level controller 44 is a multi - function circuit that can monitor and control the pulsed rf energy outputs to multiple applicators 14 . many of the sub - circuits shown in fig5 are repeated for each treatment applicator . for the sake of clarity , fig5 illustrates only one of these sub - circuits , and includes additional circuits that are common for basic treatment applicator operation . fig6 completes the overall interconnections for operation , and illustrates multiple sub - circuits required for , as an example , three treatment applicators 14 . the controlling sub - circuit that permits pulsed rf energy to reach a treatment applicator 14 is the rf power enable circuit 92 . circuit 92 is activated by an enable signal 94 from the treatment timer 48 and an enable signal 96 from the isolated power supply control 52 . when enabled , the rf power enable circuit 92 sends an rf power enable signal 98 to the rf amplifier power control 100 . circuit 100 controls the rf power level to the rf power amplifier 36 . when rf power is being transmitted to the treatment applicator pad 14 , the rf power enable circuit 92 switches on an indicator lamp 102 . forward rf power signals 104 and reflected rf power signals 106 from measuring circuit 46 are delivered to voltage comparators 108 and 110 , respectively . voltage comparators 108 and 110 allow the setting of maximum forward and reflected power levels . if either of the measured power outputs is above / below its respective set - point level , a disable signal is sent to the rf power enable logic circuit 92 , switching off rf power to one , a few or all low power rf amplifiers 36 , switching off the treatment timer 48 , and sending a signal to an optional alarm circuit 112 . during a high forward or reflected power condition , indicator flashing circuit 114 is enabled which then starts flashing the single service required led 116 . the actual rf energy that is transmitted from each treatment applicator 14 is measured by a detector located on the treatment applicator ( fig1 ). this field strength signal 118 is used to automatically regulate and control the rf output to the treatment applicator 14 . additionally , signal 118 is evaluated to determine if operation of the apparatus should be halted . specifically , comparator 120 sets a maximum field strength level , and comparator 122 sets a minimum field strength level . if the measured field strength is outside these limits , a disable signal is sent to the rf power enable logic circuit 92 , switching off rf power to all rf amplifiers 36 , switching off the treatment timer 48 , and sending a signal to an optional alarm circuit 112 . during an out - of - range condition , indicator flashing circuit 114 is enable which then starts flashing the single service required led . when the treatment applicator 14 is in place , a body proximity sensor switch ( fig9 ) is closed , and the applicator in place led 124 is illuminated . if this switch inadvertently opens , an indicator flashing circuit 126 is enabled and the check applicator led 128 flashes . fig6 describes in more detail how one embodiment of the present invention operates . initially , a crystal controlled oscillator 130 is stimulated following input of a dc supply voltage 132 . the oscillator then generates a sine wave output 134 having a frequency of about 27 . 12 mhz to a preamplifier 136 controlled by an external switch 138 so that its output 140 consists of pulses of specific duration and repetition rate as controlled by the pulse rate generator and treatment energy pulse shaper and pulse repetition controller 40 . the output of this stage of gain drives another amplification stage 142 which draws no current unless an input signal is present ( class c amplifier ). this particular feature is an important improvement in that it is one of the features allowing for the use of a very low power amplifier to drive an effective output treatment rf signal . the output 144 of amplifier stage 142 then drives two additional power amplifiers 146 , 148 , also operating as class c amplifiers . the class c operation of additional power amplifiers 146 , 148 also contributes to the ability to use low input power . the output 150 of the final amplifier is applied to the treatment applicator 14 via a coaxial cable connected to port 152 . fig6 further shows one preferred circuit for adjusting the amplifier output . field strength signal 131 is applied to one input 133 of comparator 135 . the other input 137 of comparator 135 is a preset signal or a voltage from the controller . the output 139 of comparator 135 goes to opeational amplifier 141 . the signal is then amplified further by voltage regulator 143 . voltage regulator 143 supplies dc power to the rf oscillator 130 and amplifier , thereby adjusting the output of the amplifier and , hence , the treatment dosage . fig7 is a block diagram of an embodiment of the present apparatus 10 having multiple treatment applicators 14 . as previously discussed , the power level controller 44 includes multi - tasking circuits that permit the addition and separate control of multiple treatment applicators 14 . as shown in fig7 the present invention allows for the concurrent treatment of multiple wound sites on a single patient where each wound site requires a different treatment profile . fig7 illustrates the embodiment of multiple sub - circuits that are required for , as an example , three treatment applicator pads . each autonomous circuit incorporates separate low power class c rf amplifiers 36 and forward and reflected power measuring circuits 46 . separate indicator lamps 102 , 124 , 128 are provided for applicator in place 27 , check applicator 28 , and treatment power on 29 . separately controlled rf energy pulses , which are transmitted through the individual forward and reflected power measuring circuits 46 are connected to separate treatment applicators 14 via labeled flexible cables , each applicator 14 having its own detectors and sensors ( fig9 and 10 ). from each treatment applicator 14 , separate signals from the detector and body proximity sensor are sent to individual control circuits in the power level controller 44 to independently monitor and control the rf output level radiating from each treatment applicator 14 . each control circuit of the power level controller 44 is automatically activated when a treatment applicator 14 is connected to the electromagnetic energy output device . when a treatment applicator 14 is disconnected , or if its body proximity sensor is in an open circuit condition , the associated control circuit of the power level controller 44 is automatically de - activated . fig8 is a block diagram of an isolated power supply assembly 52 of the present invention . unit 12 is powered by a source 18 , such as an internal battery pack , which can be periodically recharged using a peripheral ac line cord . an isolated power supply control 158 continuously checks the voltage from the battery pack 18 , advises the operator when it is time for re - charging , and disables all rf output functions when the battery voltage drops below a minimum level . specifically , direct battery voltage is sensed by amplifier 160 . the output of amplifier 160 is monitored by a display driver circuit 162 . circuit 162 is wired to illuminate the low led 164 when the battery voltage is below a defined voltage level and requires re - charging , to illuminate the ok led 33 when the battery voltage is at an acceptable voltage level , and to flash the high led 34 if the battery voltage is sensed to be higher than an acceptable limit . if the battery voltage is ok , an output signal 170 is sent to the power level controller 44 , enabling the rf power enable circuitry . the monitoring of battery voltage is very important because it assures that electronic circuits are being powered with adequate supply voltage , that treatment rf dosage is not compromised due to low battery voltage , and that electronic circuits ( including battery ) are not stressed or damaged due to excessively high or low battery voltage . fig9 - 13 show preferred embodiments of the applicator 14 of the present invention . as shown in fig9 - 13 , the applicator 14 is a monolithic assembly of one or more circuits having a fixed capacitance . this important feature renders the device substantially unaffected by impedance , capacitance and other related affects associated with locating an electromagnetic energy applicator in proximity to a patient &# 39 ; s body . unlike prior art devices which require manual adjustment of the capacitor ( s ) in the applicator at the treatment site , the present invention has a capacitance fixed by the manufacturer , thereby rendering the device user friendly . each applicator includes one or more circuits ( such as etched copper printed circuit , stamped wire circuit , etc .) formed on a single substrate , such as an assembly comprising one or more circuit boards . preferably , the circuits are etched or otherwise located on opposite surfaces of a single circuit board . referring to one embodiment of the present applicator shown in fig9 - 11 , applicator 14 includes a single circuit 174 that is laminated between insulating sheets of flexible kapton 178 , or similar material with high dielectric properties . circuit 174 includes an etched inductor 180 , a fixed capacitor 192 connected in parallel with inductor 180 , a signal detector 182 , and a body proximity sensor 184 . a ground plane 176 , such as a solid rf copper shield , is located directly below the first etched printed circuit 174 . circuit 174 and plane 176 are brought out to a connection interface 186 to which a flexible and shielded , multi - conductor cable 188 is permanently attached . connection to the generator unit 12 is made through connector 190 , shown in fig1 . that composite assembly defines the completed applicator 14 . fig1 and 13 show an alternative embodiment of the applicator described above having multiple circuits 174 and 177 . in the applicator 14 , the upper circuit 174 forms the secondary of an rf transformer . the primary circuit 177 is etched on the other side of this two sided board . the upper circuit 174 ( secondary ), which is a multi - turn spiral , has a fixed , surface mount capacitor 192 connected in parallel with it to form a tank circuit resonant at 27 . 12 mhz . circuit 177 ( primary ), comprising a single turn , has a fixed , surface mount capacitor connected in series . the ends of this series - resonant circuit are brought out to a connection interface 186 from which it is then connected to controller 44 and rf amplifier 36 . the function of the lc tank circuit is to radiate a pulsed rf energy in the form of a closed and concentrated rf electromagnetic energy field . circuit 174 also includes detector 182 . detector 182 is brought out to the connection interface 186 and serves as an rf energy measuring element , and as such , measures , monitors , regulates and controls the magnitude of the pulsed electromagnetic energy field , or treatment dosage , as it radiates out from the applicator . the returned signal level from detector 182 is sent to the power level controller 44 , where it is used as a feedback control signal . if at any time , detector 182 measures radiated electromagnetic energy output level above or below an acceptable rf level , a service required lamp ( fig3 ) will flash and the power level controller disables the rf energy output . it should be understood that any appropriate detector 182 , such as a germanium diode , may be used without departing from the scope of the present invention . applicator 14 also includes a body proximity sensor switch 184 . switch 184 confirms that applicator 14 is in place and attached to the patient and that the emitted pulsed rf energy field is being efficiently coupled from the applicator 14 to the patient . in use , applicator 14 is either placed under the patient , in close proximity to the patient &# 39 ; s wound , or wrapped around the limb of a patient and attached with fasteners , or is placed over a wound , again being held in place with fasteners . if applicator 14 is secured correctly , the body proximity sensor switch 184 closes , indicating to the power level controller 44 that applicator 14 is in place , and a lamp indicating applicator in place 27 is activated . if any time during treatment , the body proximity sensor switch 184 opens , indicating that applicator 14 is not in body contact , a check applicator 28 lamp flashes and the power level controller 44 disables the rf energy output . unlike many prior art devices , which are magnetic field based and , in some instances , prevent the electrical field component of the electromagnetic energy from being transmitted , the present invention relies on electrical field - based information for effective operation . electrical field strength detector 182 included in each applicator 14 produces a dc voltage as a function of the actual field strength being transmitted from applicator 14 . this dc voltage is transmitted in a reverse manner ( antidromically ) through the same coaxial cable 188 which carries the rf signal from amplifier 36 to applicator 14 . in this manner , only one cable is required to carry and process both the rf power and rf detection signals . this represents a substantial improvement over the prior art , none of which have a signal detection means at the level of the actual rf signal output , and none of which carry this detection signal over the same cable as used for transmitting the rf signal . in the rf generator 30 , this dc voltage ( detection signal 118 ) is compared to a reference dc voltage which represents the desired field strength . the output of the comparator 120 , 122 drives suitable amplifiers 100 which control the dc power supply voltage to the rf circuits , thus controlling the forward rf power . the field strength , being a function of the rf power , is thereby accurately controlled and maintained . this is a significant improvement not found in existing devices , and represents the first capability to accurately deliver , monitor and automatically control the actual rf power delivered to the tissue being treated , thereby ensuring an accurate dosage delivery and dosimetry system . the circuits are located on a single substrate , such as a circuit board . the substrate is preferably thin and may be flexible or rigid and constructed from one or more sheets . when multiple circuits are included ( fig1 and 13 ), the circuits are preferably concentrically located on the substrate . while it is not necessarily required that the circuits be exactly concentric , best results are achieved when the two circuits are as close to concentrically positioned as possible . preferably , the applicator 14 is approximately 6 inches by 8 inches by less than 1 inch thick , and is housed within a waterproof outer covering . the outer surface is water proof , bacterial resistant and designed to be placed directly on the patient or on top of any standard dressings used over the area to be treated . the generating unit 12 is about 2 . 5 inches by 5 inches by 8 inches , and has a weight of less than three pounds . in a preferred embodiment , unit 12 includes a display panel which contains the operating switch or button , a treatment time remaining display , a light which is on during treatment to notify the operator that treatment is occurring , and a service light which comes on if the unit needs servicing . unit 12 is a hand - held one , which is easily transported from site to site . applicators 14 are self supporting structures which do not require any mechanical support structure for positioning . indeed , the only means connecting the applicator 14 to the generating unit 12 is a cable . reference throughout this description to leds and other specific indicators was made for descriptive purposes only . it is understood that other indicating means for informing users of operational conditions are interchangeable with the specific indicators disclosed herein . treatment dosages of electromagnetic energy are applied as follows . the control logic circuit is programmed with treatment profiles which enable the oscillator to provide a treatment dosage of about 1 - 300 mw / cm 2 . the preferred treatment profile is administered twice a day , eight to twelve hours between treatments , for thirty minutes . indeed , the unit is preferably factory preset to deliver treatment for thirty minutes and requires no operator adjustment . when ready , the “ start / stop ” button is pressed . when this button is pressed , the indicator light indicates therapy has started and an electromagnetic energy dosage is generated and delivered to the treatment site . the electrical field at the treatment site is continuously monitored , with information being delivered back to the generating unit to control the dosage level . at the end of thirty minutes , the unit turns itself off and the power indicator light becomes dark . the following are representative examples of treatments administered using the present invention . this example describes treatment on fibroblasts , a cell type critical to the wound healing process , using the present invention . immortalized ( rat - 2 ) or primary ( human sa - 1 ) fibroblasts were plated 24 hours prior to treatment in 96 - well trays at initial densities from 500 - 10 , 000 cells per well in dulbecco &# 39 ; s modified eagle &# 39 ; s medium supplemented with high ( 10 % horse , 5 % fetal calf ) or low ( 0 , 5 % fetal calf ) serum . cells were treated either with the present invention or a control . the treatment parameters for the present invention , i . e ., pulse duration , peak power , average power ( dose ) and rate of pulse presentation , were systematically varied . optimal average power , pulse duration and repetition rate were shown to be about 32 mw / cm 2 , about 32 μs , and a mean of about 1 , 000 pps respectively . systematic changes in proliferative response as a function of changes in parameter value were found for all conditions . these results demonstrate that specific characteristics of the present invention critically influence the efficacy of response , and provide a clear picture of the optimum control logic parameters necessary for efficacious treatment of wounds in a clinical setting . this example evidences the dose - and time - dependent effects of treatment using the present invention on rat - 2 immortalized and sa - 1 human primary fibroblasts in culture . cells plated in multi - well trays at a series of densities in medium supplemented with serum at different concentrations were treated using the present invention at an average dose of between about 0 - 178 mw / cm 2 . other cells were treated with 32 mw / cm 2 for 0 to 60 minutes . after 24 hrs , cells were quantitated directly , via mitochondrial enzyme activity or crystal violet staining . when control logic circuits were preset to provide a pulse width of 32 microseconds and a pulse rate of about 600 - 1 , 000 pulses per second , proliferation was significantly enhanced ( 50 - 200 %, p & lt ; 0 . 001 ) with an ed 50 of 15 mw / cm 2 and an ed 99 of 32 mw / cm 2 . maximal proliferation occurred following 15 - 60 min treatment time with ½ - maximal effects at 8 min . these results reveal optimal and minimal doses and times of treatment to trigger proliferation response . example 3 describes a novel and proprietary method of accelerating healing to closure of chronic cutaneous wounds . it is clear that effects seen clinically and in vitro are based upon enhanced pro - proliferative effects . evidence for a specific mechanism for enhanced cell proliferation has now been obtained . rat - 2 immortalized or sa - 1 human primary fibroblasts seeded at initial densities from 500 - 10 , 000 cells per well were treated with a 32 mw / cm 2 dose or sham treated ( naïve ). at times ranging from 0 to 16 hr post treatment , medium was removed from wells containing treated cells and transferred to wells containing naïve cells . to define positive and negative controls , respectively , some treated cells were kept in medium throughout , and some naïve cells were not exposed to treated medium . at 24 hr posttreatment , all cells were crystal violet stained and quantified spectrophotometrically . modest proliferation above control levels was observed for cells treated with the present invention , even if medium was removed immediately after treatment , but larger and time - dependent increases in numbers of cells treated with the present invention were obtained if medium was left on those cells for 5 - 16 hours . proliferation of naïve cells was also observed if they received treated cell medium 0 - 16 hr after treatment . these studies show that diffusible entities promoting cell proliferation are released into and conditions cell culture medium upon treatment using the present invention . this example describes a clinical study wherein a novel , noninvasive endogenous pharmacotherapeutic wound treatment was realized . twenty high or moderate risk patients with stage ii , iii or iv pressure ulcers were entered into this study . this group presented with very severe wounds relative to the total pressure sore population . mean study wound surface area was 17 . 6 ± 2 . 1 , compared to a population average of 6 . 6 ± 1 . 3 , and all patients were severely compromised in nutritional and medical status . patients were treated for thirty minutes twice daily , with a dose equal to about 32 mw / cm 2 measured at a distance of about 6 cm from the applicator surface . all patients responded positively to the present treatment . stage ii wounds closed in about 3 - 5 weeks , compared to a norm of about 8 weeks for smaller wounds . stage iii and stage iv wounds showed similar acceleration of wound healing . average rate to closure was about 28 mm 2 / day , compared to population norms of 3 - 9 mm 2 / day for patients not treated with the present method . a highly novel finding is that tissue repair was stimulated through several layers of the wound bed , with rapid loss of necrotic tissue and simultaneous robust granulation . according to these data , the present invention reduces the time associated with wound healing by 50 %. the above examples are provided by way of illustration , and are not intended to limit the scope of the present invention . it should be understood that references to wound treatment are not limited to the induction of granulation , epitheliation and vascularization at a wound site , but also includes restoring nutrient load to a wound site , thereby inducing synthesis of growth factors , inducing the synthesis , proliferation and release of fibroblasts , epithelial , endothelial , vascular , muscle and neuronal cell types , inducing macrophage activity in a wound site , increasing mitogenic stimuli , increasing concentration of and inducing effective biological activity of growth factors within a wound site , delivering multiple growth factor therapy to a tissue , altering activity of cell cycle dependent proteins , inducing synthesis and activity of signal transduction molecules , and inducing gene expression in a tissue , among other events . further , while the present invention is described in terms of human treatment methods , it should be understood that treatment , as used herein , encompasses laboratory applications and procedures as well as veterinary applications and the like . from the foregoing , it will be appreciated by those skilled in the art that the present invention provides a particularly effective and advantageous method of and apparatus for overcoming many of the limitations associated with the treatment of patients using electromagnetic energy . it will also be readily appreciated by one with ordinary skill in the art to use the method and apparatus of the present invention in other applications , such as veterinary applications . although certain presently preferred embodiments of the present invention have been specifically described herein , it will be apparent to those skilled in the art to which the invention pertains that variations and modifications of the various embodiments shown and described herein may be made without departing from the spirit and scope of the invention .
a method of and apparatus for the treatment of chronic wounds using pulsed electromagnetic energy provides a constant , known and replicable dosage output which remains unaffected by the capacitance of the patient &# 39 ; s body . the apparatus is simple to operate , requiring little operator training or interaction with the apparatus . all specifications of the apparatus relating to the generation and emission of electromagnetic energy are fixed , with the specifications based on actual scientific studies of the various technical parameters involved , such as pulse width and rf dosage . the apparatus includes a pulsed electromagnetic energy generator , a power level controller and one or more thin applicators which can be flexible . the applicators are located immediately adjacent to the patient &# 39 ; s body , without the aid of a support member or removal of any dressings or bandages . the generator , which can be battery - operated , is a low power , programmable compact unit whose output is controlled by multiple control circuits for ensuring accurate treatment dosage , for confirming that the treatment was properly administered , and for disabling the generator when appropriate . the generator output is automatically adjusted in response to instructions from the field strength sensor located on or near the applicator . multiple applicators selected to operate simultaneously at different treatment dosage levels are connected to the generator by multi - conductor cables and readily located directly on the treatment area . each applicator is a pad including etched printed circuits . the circuits are matched and pre - tuned . an applicator - to - patient proximity detector is also incorporated in or on each applicator and connected to the generator via a power controller to provide for direct monitoring of the treatment site and precise control of treatment dosage .