Microelectric apparatus for the antisepsis, promulgation of healing and analgesia of wound and chronic skin ulcers

A small, handheld, microelectric, direct current generator with a low frequency modality is applied directly to a wound site through a composite wound covering or dressing. An electric potential difference is established between an anode and cathode of the composite wound dressing. Wound healing is facilitated by the biostimulatory effect of the applied microelectric current on adenosine triphosphate production (ATP), cell membrane transport of amino acids and protein synthesis. The microelectric currents applied through the composite wound dressing, promulgate antisepsis, interfere with the neurological transmission of pain signals and concomitantly stimulate the release of endorphins which helps to relieve the pain associated with wounds, ulcers and other tissue injuries.

BACKGROUND OF THE INVENTION 
1. Field of the Invention 
This invention is directed to a method and apparatus for healing wounds. 
More specifically, to a method and apparatus for healing wounds by an 
application of low frequency microelectric current. 
Chronic wounds and skin ulcers are, typically, contaminated with a variety 
of microorganisms, both pathogenic and non-pathogenic types. The 
non-pathogenic types of microorganisms constitute the normal flora of 
intact skin and may become pathogenic when their numbers overwhelm the 
natural host defenses in the wound environment and subsequently cause 
infection. Becker, G. D.: "Identification and Management of the Patient at 
High Risk for Wound Infection". Head Neck Surg Jan/Feb: 205-210, 1986. 
Quantitatively, it has been shown by Kucan, J. O. et al in "Comparisons of 
Silver Sulfadiazine and Physiologic Saline in the Treatment of Chronic 
Pressure Ulcers", Amer Ger Soc 29:232-235, 1981, that open wounds can 
maintain a bioburden of approximately 10.sup.5 microorganisms per gram of 
tissue without clinical manifestation of infection. However, a bioburden 
of greater than 10.sup.5 is a significant challenge for the local wound 
tissue defenses. Consequently, a bioburden of 10.sup.6 microorganisms per 
gram will often result in wound infection. Robson, M. C. et al., 
"Bacterial Quantification of Open Wounds", Military Medicine 134:19-24, 
1969. 
Wounds that are heavily contaminated by microorganisms, but not clinically 
infected, are often characterized by a prolonged period of inflammation as 
well as a delay in wound repair and healing. Micro-organisms that 
contaminate wounds have been implicated as an important factor in the 
retardation of wound healing by interfering with leukocyte phagocytosis 
and also by the depletion of nutrients and oxygen required for normal 
tissue granulation. Ree, B. R. et al., "Cutaneous Tissue Repair: Practical 
Implication of Current Knowledge, Part II", Journal of the American 
Academy of Dermatology 13(6): 919-941, 1985. 
Historically, wounds have been cleansed and disinfected with a host of 
different types of antiseptic agents ranging from acetic acid to 
halogen-based solutions such as complexed iodine. While topical antiseptic 
agents have the recognized ability to either inhibit or destroy infection 
producing microorganisms, they also induce chemical trauma and necrosis of 
the host defense cells, such as macrophages, when used directly in the 
wound site. Branemark, P. I. et al., "Tissue Injury Caused by Wound 
Disinfectants", Bone Joint Surg Am 49:48-6.2, 1967 and Lineweaver, W. et 
al., "Topical Antimicrobial Toxicity", Arch Surg 120:267-270, 1985. 
Furthermore, topical antiseptic agents, which are known to be severe 
cytotoxins, impinge dramatically upon the wound-healing processes and 
greatly impair the host defense mechanism. Viljanto, "Disinfection of 
Surgical Wounds Without Inhibition of Normal Wound Healing", Arch Surg 
115:253-256, 1980. 
Alternatively, minute concentrations of silver ions in solution or in the 
wound environment demonstrate a pronounced micro-biocidal effect without 
the corresponding cytotoxic properties generally associated with 
antiseptic and other non-biocompatible agents used to facilitate wound 
antisepsis. 
Wound healing is also influenced by other factors and interventional 
methods including the application of low amperage microcurrents. Clinical 
investigators have established that electro-stimulation can affect every 
phase of wound healing. Becker, R. "The Direct Current Control System: A 
Link Between Environment and Organism", N.Y. State, Med 62-1169-1176, 
1962; Becker, R., "Electrical Control of Growth Processes", Med Times 
95:657-669, 1967a,; and Becker, R. et al., "Method for Producing Cellular 
Differentiation by Means of Very Small Electrical Currents", Trans N.Y. 
Acad Sci 29:606-515, 1967b. 
Direct galvanic or low intensity direct current delivered to the wound 
site, in a steady state or as pulsed electrical stimulation, at current 
intensities between 0 to 1000 microamperes increased adenosine 
triphosphate (ATP) levels and improved protein synthesis. Wolcott, L. et 
al., "Accelerated Healing of Skin Ulcers by Electrotherapy: Preliminary 
Clinical Result", South Med 62:795-801, 1969. 
The process by which ATP synthesis occurs has been postulated by numerous 
investigators: Davis, R. V., "Therapeutic Modalities for the Clinical 
Health Sciences", 1st ed., 1983, Copyright, Library of Congress 
TXU-389-661; Griffin, J. E. et al., "Physical Agents for Physical 
Therapists", 2nd ed., Springfield, Charles C. Thomas, 1982; Krusen et al., 
"Handbook of Physical Medicine & Rehabilitation", 2nd ed., Philadelphia, 
W. B. Saunders Company, 1971: and Schriber W. A., "A Manual of 
Electrotherapy", 4th ed., Philadelphia, Lea & Feiblger, 1975. 
In this process, electrons stimulated by microcurrents react with water 
molecules at the anode to produce positively charged hydrogen ions and in 
similar fashion, negatively charged hydroxyl ions are formed at the 
cathode. An electrical potential with a corresponding proton gradient is 
created between the anodic and cathodic poles, as well as between the cell 
wall of the tissue and intracellular fluid. When moving electrically 
charged hydrogen ions transverse the tissue cell wall and encounter the 
membrane of the mitochondria, (an intracellular organelle), with its 
stores of Adenosine triphosphatase, (the enzymatic catalyst of ATP 
production), the Adenosine triphosphatase is activated to enhance the 
manufacture of ATP. ATP is utilized as the energy resource for the 
endothermic synthesis of important proteins. 
Amino acids, the building blocks of proteins, are transported by the 
electrical gradients through the mitochondrial membrane and synthesized 
into proteins by means of energy made available by ATP. 
Physiological evidence of the biostimulatory effects of microcurrent 
application to wounds was reported by Alaverez, Om., et al., 1983, J. 
Invest. Dermatology, 81(2), 144, where they observed "a marked increase in 
the synthesis of collagen and the rate of epithelial regeneration, which 
are key aspects of wound healing". 
In a carefully controlled in-vitro study, Nessler, J. P., Mass. O.P. 
Clinical Orth, Rel, Res., (217), 303 demonstrated that "transected rabbit 
tendons grown in culture medium responded to microcurrent stimulation of 7 
uA with a 91% higher uptake of proline and 255% greater hydroxyproline 
activity, both of which are important biochemical constituents of tissue 
repair, than the unstimulated control". 
Numerous other investigators have found that low intensity direct current 
enhanced the wound healing process. Carley, P. J. et al., 1985, Arch Phys 
Med Rehab, 66, (7), 443-446, described a "150-250% improvement in the rate 
of healing decubitus". Gault, W. et al., 1976, Physical Therapy, 56 (3) 
265, "treated 106 ischemic skin ulcers with microcurrents which ranged 
from 200-800 uA and found that the ulcers treated healed twice as fast as 
those that were untreated". Wolcott, L. D. et al., 1969, South Med J., 
62,796-801 "treated a group of 67 patients with low intensity direct 
electrical currents and reported an increased in the rate of healing over 
the control group. " 
Electro-analgesis has been known for a number of years. Medical devices 
which are designed for the application of small electrical currents to the 
human body subscribe to the theory of Transcutaneous Electrical Nerve 
Stimulation (TENS) or Electro Galvanic Stimulation (EGS) to afford pain 
relief without the use of analgesic drugs which have a potential for 
patient misuse and habituation. In theory and practice, electrocurrents in 
micro- or milli-ampere range are applied to the body, through a pair of 
oppositely charged skin electrodes, which block the neuro-transmission of 
pain signals and/or reduce the perception of pain by directly influencing 
the release of endorphins, a natural analgesic produced endogenously. 
Goldstein, A., "Opid Peptides (Endorphins) in Pituitary and Brain", 
Science, 1976:193:1081-1086 and Guillenum, R., "Endorphins, Brain Peptides 
that Act like Opiates", N. Eng J Med 1977, 4:226-228. 
Holloway, A. G., "Lower Leg Ulcers: An Overview", Chronic Wound Care: 
Health Management Publications, Inc., 1990, specifically states that 
"Characteristic symptoms of wounds classified as arterial ulcers generally 
involve pain." 
Partial thickness wounds accompanied by inflammation and edema are 
uniformly painful. Experimentally, it has been proven that microampere 
electrical stimulation does mitigate pain secondary to tissue injury 
inasmuch as it has been shown that naloxone hydrochloride will block the 
palliative effects of the low level electrical stimulation by interfering 
with the opiate receptor sites in the brain. Sjolund, B. et al., "Electro 
Acupuncture and Endogenous Morphines", Lancet 1976:2:1085 and Hosobachi, 
Y. et al., "Pain Relief By Electrical Stimulation of the Central Gray 
Matter in Humans and Its Reversal by Naloxone", Science 1977:197:183-186. 
SUMMARY OF THE INVENTION 
A small, handheld, microelectric, direct current generator produces a 
current having an amplitude of about 0 to 1000 microamperes with a 
frequency range of about 0.3 to 292 pulses per second. The generator is 
selectively connected to a device or apparatus which operates as a wound 
dressing or covering. The device comprises an electro-conductive hydrogel 
such as a hydrophilic, adhesive polymer which is adhered to a flexible 
plastic or non-woven support layer. A first electrode, consisting of a 
pure silver anode, passes through the support layer and the hydrogel. A 
second electrode, consisting of a base metal cathode, surrounds the anode 
and is mounted on the support layer which is an electro-conductive, 
hydrophilic, adhesive polymer. The cathode does not pass completely 
through the hydrogel. The hydrogel is formed in two concentric rings, one 
of which surrounds the anode and the other one of which engages the 
cathode. 
The generator establishes an electric potential differential between the 
anode and cathode of the composite wound dressing apparatus. Consequently, 
the microelectrical stimulation of the anode readily ionizes the pure 
silver into positively charged particles which are driven, by the 
microcurrent, in the direction of the cathode. The charged silver ions 
exert a lethal effect upon bacteria and other microorganisms that 
contaminate the wound environment through a process called oligodynamic 
action. 
Wound healing is facilitated by the biostimulatory effect of the applied 
microelectric current on adenosine triphosphate (ATP) production, cell 
membrane transport of amino acids and protein synthesis. 
Microelectric currents applied through the composite wound dressing also 
interfere with the neurological transmission of pain signals and 
concomitantly stimulate the release of endorphins, the body's naturally 
occurring analgesic, which helps to relieve the pain associated with 
wounds, ulcers and other tissue injuries.

DESCRIPTION OF THE INVENTION 
Referring now to FIGS. 1, 2 and 3 concurrently, there is shown a preferred 
embodiment of the applicator apparatus of the instant invention. 
The applicator apparatus consists of a bipolar, electro-stimulating pad 
(ESP) 100 configured as a circle or an ellipse. The ESP 100 includes a 
dorsal support surface layer 105 which is composed of an adhesive-coated, 
electrically inert, flexible plastic or non-woven cloth material. The 
support layer 105 is laminated to contact surface layers 106 and 107. The 
layers 106 and 107 are constituted of an electrically-conductive hydrogel 
polymer such As commonly used in the art. The polymer layers embody the 
surfaces that abut the integument and/or wound opening when in use. The 
hydrogel polymer exhibits both electro-conductive and adhesive properties. 
Thus, when applied to a wound site, the hydrogel polymer adheres firmly to 
the intact skin surrounding the wound. 
As seen in the Figures, the layers 106 and 107 are arranged in concentric 
rings with layer 106 encircling layer 107. 
In an alternative configuration, the flexible plastic or non-woven backing 
(FIG. 1) may be radially extended beyond the circumference described by 
the hydrogel polymer to thereby provide an additional adhesive surface to 
secure the ESP 100 to the wound margin. 
The anode 101 is a single pole located at the center of the ESP 100. The 
anode 101 is fabricated of pure silver. In a preferred embodiment, the 
anode 101 includes a flat surface 110 at the inward end thereof. An 
attaching clip, stud or terminal 103 is provided at the outward end of 
anode 101. An outer securement surface 111 is provided at the outward end 
of anode 101. The cathode 102 consists of an electrically conductive ring 
disposed at the circumference of the ESP 100. The peripheral ring of the 
cathode 102 substantially surrounds the anode 101. The anode 101 and 
cathode 102 are connected to separate electro-conductive terminal 103 and 
terminal Or stud 104 through the composite materials of the ESP 100 and 
attached at the dorsal surface 105 of the ESP 100. These terminals 103, 
104 are provided as the coupling points for a direct current microampere 
electrical generator discussed infra. 
The attaching stud 103 for the silver anode 101 and the attaching stud 104 
for the metallic cathode 102 are punched through the composite materials 
of the ESP 100 and secured in position by swaging them together with 
electrical terminal snap connectors. The cathode stud 104 is joined to the 
cathode ring 102 and substantially embedded in the outer ring 106 of 
polymer. The anode stud 103 passes completely through the inner ring 107 
of the polymer. The inward surface 110 of the anode stud 103 is arranged 
to make contact with the surface of the patient. 
Referring now to FIGS. 4 and 5, there is shown a representative small, 
handheld, microampere direct current unit 400 with a selectable range of 
microcurrent output (for example, 0 to 1000 uA). The handheld unit 400 
includes a generator 402 capable of operation in either steady state or 
pulsed frequency (for example, 0.3 to 292 pulses per second). The unit 
additionally includes a high frequency generator or oscillator 605 for 
this specific purpose. Both generators 402 and 405 are attached to the 
electrical terminal snap connectors 103 and 104, shown in FIG. 1, 
utilizing, for example, low resistance, shielded wires (not shown) fitted 
with appropriate pin and snap connectors at the ends thereof. Easy 
attachment is facilitated by inserting the pins into jacks 403 and 404 
provided in the unit 400. The snap connectors of the wires are attached to 
the ESP 100 by way of the snap connectors 103 and 104. 
By operation of the touch contact switches or control keys 406, 407, the 
output frequency of the signal at jacks 403 and 404 can be controlled. 
Also, mode key 408 provides manual mode selection capabilities. The output 
frequency of the output signal is displayed at the display 411. 
Additionally, light indicator 412 provides a visual power on/off 
indication. 
Referring concurrently to FIG. 5, there is shown a block diagram of circuit 
500 of handheld unit 400. The microampere circuit 500 is electrically 
driven by one 9 volt alkaline battery 502. The microcurrent circuit 500 
has the capability to be used as a DC dual channel steady state continuous 
or pulsed current stimulation device with current ranges from 1 uA to 1000 
uA. The device is controlled by a microprocessor 601 that is, also, 
capable of being used both as a preset specific frequency device or as a 
variable frequency device by the use of the mode selector switch or key 
408. Additionally, a mode control 508 provides the device the capabilities 
of varying the frequencies from 0.3 to 292 Hz. The mode key switch 408 
selects and adjusts current frequency and amplitude together with arrow 
keys 406 and 407. This allows a manual selection for the user. 
An electronic digital readout or LCD display control 515 monitors and 
displays the microampere output and frequency when in use. In the 
embodiment shown, the display 411 can be a liquid crystal display (LCD) 
which includes a latch buffer 517. The circuit 500 of the microcurrent 
generator 400 is housed and electrically isolated in the small handheld 
unit shown in FIG. 4. 
Referring now to FIGS. 5 and 6, there is shown a block diagram of a 
processor control circuit 600 of the micro-processor 510. 
The circuit 600 includes a micro-controller 601 of any conventional 
configuration. Typically, a preprogrammed 87C51 micro-controller is 
utilized. This unit receives and processes instructions from 604 (mode 
key, .uparw.key, .dwnarw.key) and processes the instructions as "mode 
control" (+, -, +/-), frequency generator, channel 1 amplitude, channel 2 
amplitude and controls the LCD. 
A regulated power supply 603 is connected to the micro-controller 601. The 
power supply 603 also provides power to other portions of the circuit 600 
as is appropriate. The regulated power supply 603 provides a regulated 
supply signal to the circuit 600. 
An EEPROM 602 is connected to micro-controller 601. The EEPROM 602 is an 
electrically erasable, programmable, read-only memory which provides 
signals to the micro-controller 601. The EEPROM 602 is-also used as a 
memory for the micro-controller 601. The EEPROM stores signals therein 
which are representative of the operation of the circuit. The last control 
settings utilized for frequency and wave form are stored and referenced 
until new parameters are manually entered through control keys 510, 512 
and 514. 
An oscillator 605 is connected to the micro-controller 601 to provide a 
suitable frequency signal thereto. The oscillator 605 is any suitable 
Oscillator such as a crystal-controlled oscillator or the like which can 
provide a high frequency signal to the micro-controller 601. Depending 
upon the operation of the micro-controller 601, the frequency signal from 
oscillator 605 can be divided or otherwise reduced to produce any number 
of desirable frequency signals. 
A key control circuit 604 is connected to provide control signals to the 
micro-controller 601 in order to select the frequency of the signals 
supplied thereby. The key control device 604 is connected to the 
micro-controller 601 to determine the mode of operation of the 
micro-controller and, through switches or the like, is then able to 
increase or decrease the output signal produced by the micro-controller 
601. 
The liquid crystal display device 411 is connected to the micro-controller 
601. The LCD device 411 displays the frequency of the signal which is 
being generated by micro-controller 601 as a result of the operation of 
the oscillator 605 and the key control 604. 
The mode control 508 is connected to an output of micro-controller 601 to 
select the mode of operation of the output signal. The mode control 508 
receives the signal from the micro-controller 601 to determine what mode 
of operation is to be provided. 
A O/P driver 607 is connected to an output of the micro-controller 601 and 
an output of the mode controller 508. The driver 607 is connected to 
supply output signals to the ESP device 100 noted above in accordance with 
the signal supplied thereto. 
The driver 607 then supplies signals to the ESP device 100 described above 
in response to signals supplied to driver 607 by micro-controller 601. 
Referring now to FIG. 7A, there is shown in greater detail a portion of the 
circuit shown in FIG. 6. In particular, the micro-controller 601 is 
connected to the LCD display 411 by means of a plurality of lead lines. In 
particular, there are shown a number of voltage dividers which are 
connected to supply specific voltages to certain terminals of the LCD. The 
other terminals are connected to individual terminals or ports of the 
micro-controller 601 in order to provide specific signals to specific 
symbols, characters or portions thereof in the display 411. 
The display 411 is conventional in design and provides the output display 
indicator 412 which is representative of the signal being provided to the 
output network connected to the ESP device 100. Thus, the LCD 411 
includes, in the embodiment illustrated, a seven-segment display for each 
character and is operated in a conventional manner in response to the 
signals from the micro-controller. 
The key controller 604 comprises a plurality of switches or keys 408, 407 
and 406 which are connected between ground and, effectively, the control 
voltage provided by the regulated power supply 603. The switches can be 
any type of switch including pressure switches, push buttons or the like 
mounted on the front face of handheld unit 400. Thus, mode switch 408, 
when operated, selects the mode of operation of the device. For example, 
mode key 604 can select any of the following when pushed: Mode control 508 
selects polarity, positive (+), negative (-), bi-polar (+/-); frequency 
control 402 selects range from 0.3-300 HZ; or amplitude control 510 
selects range from 0-100 microampere with a resolution of 5 microampere. 
For example, whenever the decrementing switch 407 is operated, the signal 
supplied by the micro-controller 601 is decremented by a factor of 1 Hz. 
(i.e. cycles per second). Conversely, when the incrementing switch 406 is 
activated, the frequency of the signal supplied by micro-controller 601 is 
increased by 1 Hz. 
The regulated power supply 603 comprises the battery 502 which is connected 
to a voltage controller device which regulates the battery voltage within 
+ or -0.5 volts. Thus, when the battery voltage output deteriorates to a 
level of approximately 5.5 volts, the regulator device is turned off so 
that no voltage is supplied at the output terminal VCC. Thus, the system 
is shut down to avoid inaccurate operation due to a low voltage problem. 
As shown in FIG. 7B, shunt capacitors are provided at the input and output 
terminals of the voltage regulator device 603 so that spikes or noise 
signals are not supplied to the circuit 600. 
As noted, the regulated power supply 603 is connected to the 
micro-controller 601 by means of an additional filter network comprising a 
coupling Capacitor and an impedance path to ground which prevents 
inappropriate signals from being supplied to the micro-controller. 
The EEPROM 602 is connected to appropriate terminals at the 
micro-controller. The EEPROM 602 also receives the control voltage VCC. 
Consequently, the regulated power supply 603 is desirable to prevent 
spurious signals from being supplied to the EEPROM 602. 
The EEPROM 602 is operated to include signals representative of current, 
frequency and waveform. EEPROM 602 saves in short term memory the 
frequency and waveform (+, -, +/-) settings which may be read by the 
micro-controller 601. The amplitude is not stored and must be set. Thus, 
the signals are supplied to the micro-controller 601 and vice versa in 
order to control the operation of the circuit. 
The oscillator 605 is also connected to supply high frequency signals on 
the order to 6 MHz. to the micro-controller. These signals are supplied 
via coupling capacitors. The signals are related to a common ground 
wherein a bipolar frequency signal is supplied to the micro-controller. 
Also referring to FIG. 7B, there is shown a quad bilateral switch circuit 
or O/P driver 607 which is, typically, a model 4066 manufactured by any of 
the current manufacturers, such as Motorola, NEC or others. 
The circuit 607 is connected directly to the micro-controller 601 to 
receive signals which represent the output waveform. Likewise, the circuit 
607 is connected to the micro-controller circuit via the driver circuit 
comprising transistors Q1 and Q2, respectively. These transistors are 
controlled by the signals generated in the micro-controller 601 to effect 
operation of the 607 circuit. 
At each of the outputs of the 607 circuit are provided a pair of Darlington 
circuits Comprising transistors Q3 through Q10, inclusive. Each Of the 
Darlington pairs is connected to one terminal of the primary winding of a 
transformer T1 or T2. The opposite ends of the primary winding is 
connected to another of the Darlington pairs. The primary winding is 
center-tap Connected to the bias voltage VCC, wherein the operation of the 
driver circuit is to provide a push-pull operation in the primary winding 
of the respective transformer. 
The output of the respective transformers are connected to appropriate 
leads or coupling lines which are then connected to the anode 101 and 
cathode 102 of the ESP device 100, respectively. 
Irrespective of which control circuit is utilized, the ESP can be used 
topically to Control clinically diagnosed or manifest wound infections, as 
well as to significantly reduce the large numbers of microorganisms that 
constitute the biological burden on the living tissue of an open chronic 
wound. In practice, the ESP 100 is placed directly over the wound cavity 
or affected area and secured by the adhesive hydrogel polymer rings 
106/107. Alternatively, the ESP can be secured to the intact skin 
surrounding the wound margin by adhesive tape. The microcurrent generator 
400 is attached to the ESP via the connecting wires by coupling the 
positive conducting current wire to the centrally located silver anode 
snap connector. In similar fashion, contact is established between the 
negative conducting current wire and the cathode. 
The small handheld unit 400 is then activated by the ON/OFF switch and the 
microcurrent is adjusted between 0-1000 uA by changing the position of the 
variable current switch. The output current is monitored on the electronic 
digital display 411. If pulsed direct current is preferred, the variable 
pulse frequency modulation switch is activated, by way of the mode control 
508, and the frequency to be used is selected and monitored through the 
display 411. 
Upon application of a microcurrent to the wound through the ESP 100, the 
silver of the anode 101 is ionized, commensurate with the intensity of the 
microampere current. Subsequently, silver ions are driven toward the 
cathode 102 along the lines of the electrical potential gradient which is 
equal in all directions from the anode 101 because of the annular 
configuration of the cathode 102. 
Small amounts of the positively charged silver ions (silver ion 
concentrations estimated to be as low as 0.5 ppm) exert a bactericidal 
effect upon most microorganisms contaminating the wound bed by means of 
oligodynamic action, thereby affecting wound antisepsis. 
Concurrently, the applied microcurrents stimulate the production of protons 
at the anode 101, with a corresponding proton gradient that is formed 
across the tissue cell wall, which also involves the intracellular fluid. 
Protons which traverse the intracellular fluid and encounter the 
mitochondrial membrane chemically bind adenosine triphosphate (ATP). The 
formed ATP then acts as the energy resource for the intracellular 
synthesis of proteins from the available essential amino acids that have 
been transported across the mitochondrial membrane. The synthesized 
proteins constitute the building blocks of living tissue which ultimately 
are the most important ingredients in the wound healing process. 
Pain and local discomfort is commonly associated with most wounds and local 
tissue trauma. Pulsed microcurrents through the ESP device 100 provides 
temporary analgesia by interrupting the transmission of pain signals 
across the neurons and also by stimulating the release of endorphins, the 
body's own pain killers. 
All three actions: antisepsis, wound healing and analgesia, occur 
simultaneously when microcurrents are applied through the ESP device 100 
to a wound or irritated integument. 
Some chronic wounds or ulcers develop as a consequence of a primary disease 
process. For example, those persons afflicted with diabetes typically 
exhibit very poor peripheral vascular circulation, especially of the lower 
extremities. Skin breakdown, chronic wounds and ulcers are common among 
active, insulin-dependent diabetics. Most diabetic foot and leg ulcers are 
slow to heal and quite prone to serious infections, many of which result 
in life-threatening gangrene that can only be resolved, in many cases, by 
surgical amputation of the limb. Administration of microcurrents, through 
the ESP device 100, to a bacterially contaminated diabetic leg or foot 
ulcer can provide a high degree of prophylaxis against infection, as well 
as stimulate the body's tissue to manufacture ATP, an essential 
requirement of protein synthesis and wound healing. 
Venous stasis ulcers are secondary to venous stasis disease which is a 
consequence of prolonged venous hypertension which is traceable to a 
condition known as deep vein thrombosis. Chronic pain invariably 
accompanies venous stasis ulcers and adds to the misery of the patient. 
Long-standing venous stasis ulcers, including the intermittent cycle of 
ulcer formation and healing, predisposes the patient to poor capillary 
perfusion and progressive ulceration. Application of microcurrents in a 
pulsed direct current mode will afford the patient some palliative control 
of the pain associated with venous stasis ulcers and also impart some of 
the other benefits, described earlier, with the use of low intensity 
currents. 
Patients with surgical wounds and incisions historically are treated with 
strong analgesics and/or opiate drugs to help mitigate the pain and 
discomfort which is intimately bound to virtually all post-surgical 
trauma. 
The use of the ESP device 100 can help to reduce the requirement for the 
amount of habit-forming analgesics required to provide relief from pain 
associated with post-surgical wounds and also to provide a means to reduce 
the great numbers of infection-causing bacteria. 
ESP 100 represents a unique combination of therapy which carefully 
addresses the major aspects of wound care. 
Thus, there is shown and described a unique design and concept of a method 
and apparatus for healing of wounds using microelectric currents or 
prescribed frequencies. The particular configuration shown and described 
herein relates to the application of a microelectric current from a 
handheld generator to a wound site through a composite wound dressing 
device. While this description is directed to particular embodiments, it 
is understood that those skilled in the art may conceive other 
modifications, variations or changes to the specific embodiments shown and 
described herein. Any such modifications, variations or changes which fall 
within the purview of this description are intended to be included therein 
as well. It is understood that the description herein is intended to be 
illustrative only and is not intended to be limited only by the claims 
appended hereto.