Patent Abstract:
A bio-implantable electrochemical cell system for active implantable medical devices. In one embodiment, the fuel cell includes an electrode structure consisting of immobilized anode and cathode enzymes deposited on nanostructured high-surface-area metal nanowires or carbon nanotube electrodes. The anode enzyme comprises immobilized glucose oxidase and the cathode enzyme comprises immobilized laccase. Glucose is oxidized at the surface of the anode and oxygen is reduced at the surface of the cathode. The coupled glucose oxidation-oxygen reduction reactions provide a self-generating current source. In another embodiment, the nanowires or carbon nanotubes, along with the adjacent surface anode and cathode electrodes, are coated with immobilized glucose oxidase and immobilized laccase containing biocolloidal substrates, respectively. This results in the precise construction of an enzyme architecture with control at the molecular level, while increasing the reactive surface area and corresponding output power by at least two orders of magnitude.

Full Description:
BACKGROUND OF THE INVENTION  
       [0001]     1. Field of the Invention  
         [0002]     The present invention relates to implantable power sources, and more particularly to a bio-implantable electrochemical cell system for providing high power for active implantable medical devices.  
         [0003]     2. Description of the Prior Art  
         [0004]     Implantable power sources for cardiac pacemakers, defibrillators, implantable diffusion pumps, neurostimulators and other active implantable medical devices have contributed to the health of millions of patients during the past few decades. During this same period, there have been increasing pressures to reduce healthcare costs by reducing hospital and in-patient stays without compromising the quality of patient care. The result has been an increase in the numbers of out-patients who rely on active implantable medical devices to maintain and/or improve their health.  
         [0005]     An active implantable medical device is defined as any active device which is intended to be totally or partially introduced, surgically or medically, into the human body or by medical intervention into a natural orifice, and which is intended to remain after the procedure.  
         [0006]     For example, a cardiac pacemaker is an active implantable medical device that uses a steady electrical pulse to regulate the beating of the human heart. The first cardiac pacemaker was invented by John Hopps in 1950, but this device was far too large to be implanted inside the human body. The first implantable cardiac pacemaker and corrosion-free lithium battery was invented by Wilson Greatbatch in the late 1950&#39;s (U.S. Pat. No. 3,057,356 issued Oct. 9, 1962).  
         [0007]     The cardiac pacemaker is implanted in the chest cavity, near the heart, and is used to correct slow ventricular rate (bradycardia), high ventricular rate (atrial fibrillation or flutter), and arrhythmia. Patients having these heart pacing abnormalities have a defective sinoatrial node and are unable to maintain a regular heartbeat. Modern cardiac pacemakers control both the ventricles and the atria of the heart, by timing the contraction of the atria to proceed that of the ventricles, thereby improving the pumping efficiency of the heart. These devices are particularly useful for patients suffering from congestive heart failure.  
         [0008]     All cardiac pacemakers require a source of electrical power to function. Most cardiac pacemakers use implantable lithium batteries that are implanted with the pacemaker; however, they have the disadvantage of requiring an additional surgery every 24 months to replace the battery. The power requirements of the cardiac pacemaker are typically in the microampere range.  
         [0009]     By contrast, the coronary stent is an example of a passive implantable medical device. A coronary stent consists of metal wires, usually stainless steel, nitinol or other metal alloy, that is used to remove blockage of coronary arteries. The stent is wrapped around a deflated balloon and surgically advanced to the site of the coronary artery blockage. The balloon is then inflated and the stent expands, pressing the blockage tissue against the wall of the artery and restoring the blood flow to the heart. In this procedure, called balloon angioplasty, there is no power source required for insertion of the coronary stent.  
         [0010]     Another example of an active implantable medical device is the implantable drug infusion pump, which delivers therapeutic plasma levels of an active drug to a target organ or body compartment for prolonged periods of time. There exist both programmable and non-programmable drug infusion pumps. In the former the bulk drug flow is generated by direct mechanical action powered by a battery, while in the latter the flow is generated by a fluorocarbon propellant. The pump is surgically implanted in a subcutaneous pocket and connects to a dedicated catheter that has been placed in the appropriate compartment. Constant or variable rates of infusion are possible over long periods of time with minimal human intervention; however, in the case of programmable drug infusion pumps, the battery must eventually be replaced. The power requirements of the implantable drug infusion pump are typically in the milliampere range.  
         [0011]     An example of an implantable drug infusion pump is the implantable insulin pump used to deliver insulin into patients with diabetes, in order to maintain their blood sugar, or glucose, at a constant level.  
         [0012]     Most active implantable medical devices have been powered primarily by lithium/iodine or lithium/carbon monoflouride batteries. Lithium/iodine batteries are typically used to generate currents in the microampere range, while lithium/carbon monoflouride batteries can generate currents in the milliampere range. During the last few decades, the size of active implantable medical devices and the power consumption of their complementary metal-oxide semiconductor (CMOS) electronic circuits have been continually reduced. At the same time, the size and weight of the power sources for these devices have not been proportionally reduced, primarily due to the difficulty of miniaturizing the case and seal of the power source. At the same time, the case and seal are necessary for a battery since the lithium anode will oxidize in a humid environment, and the alkakine electrolyte of zinc-silver oxide batteries is highly corrosive.  
         [0013]     As mentioned above, another difficulty with batteries as a power source for active implantable medical devices is the requirement of periodic recharging or replacement. This is particularly difficult in situations where the battery is contained within the implanted device, because surgery is required to remove and replace the battery. The alternative of having the power source located outside the body is equally problematic, since the point where the power leads enter the body is also subject to infection. Any situation in which an invasive procedure is used can lead to infection and other more serious medical complications.  
         [0014]     The power requirements of different implantable devices vary from microamperes for cardiac pacemakers to milliamperes for drug infusion pumps and neurostimulators to amperes for cardiac defibrillators. These increasing power requirements lead directly to an increasing size and weight in power source that makes implanting of the latter impossible.  
         [0015]     In addition to the above-discussed existing active implantable medical devices, the nascent fields of nanotechnology and nanomedicine are focused on developing and deploying implantable, molecular-scale machines and devices for the prevention and treatment of disease in the human body. For example, the most elemental nanomedical devices will be used to diagnose illness by monitoring the internal chemistry of the body. Currently under development by many researchers are mobile nanorobots, equipped with wireless transmitters, that might circulate in the blood and lymph systems and send out warnings when chemical imbalances occur or worsen. Similarly, fixed nanomachines may be implanted in the nervous system to monitor pulse, brain wave activity, and other neurological functions.  
         [0016]     A more advanced use of nanotechnology in medicine might be the use of implanted, molecular-sized devices to dispense drugs or hormones at the cellular level. Ultimately artificial antibodies, artificial red and white blood cells, and antiviral nanorobots might be developed and deployed.  
         [0017]     The most advanced nanomedicine might involve the use of nanorobots as miniature surgeons. The active implanted devices might repair damaged cells; or get inside of cells to replace or assist damaged intracellular structures. At the extreme, nanomachines might replicate themselves or correct genetic deficiencies by altering or replacing DNA molecules.  
         [0018]     Most of these new nanotechnology devices will be active implantable devices that will require a miniature, implantable power source that does not need to be recharged or otherwise maintained.  
         [0019]     Accordingly, there is a need for a bio-implantable electrochemical cell that derives its power from blood or other body fluids, has no mechanical or moving parts, has no hazardous electrolytes requiring a sealed case, is biologically compatible, and does not require external recharging or replenishment.  
       SUMMARY OF THE INVENTION  
       [0020]     The present invention is directed to a bio-implantable electrochemical cell system for providing high power for active implantable medical devices. The electrochemical cell of the present invention provides an order of magnitude improvement in power density (1,000 to 10,000 μW cm −2 ) over existing glucose/oxygen fuel cells, with a total output power of 1,000 to 10,000 μW. The output of the present invention is sufficient to power many conventional active implantable medical devices, including cardiac pacemakers, neurostimulators, and drug infusion pumps.  
         [0021]     In a first embodiment of the present invention, the electrochemical cell includes a novel electrode structure consisting of immobilized anode and cathode enzymes deposited on nanostructured high-surface-area gold electrodes. The anode enzyme may comprise immobilized glucose oxidase and the cathode enzyme may comprise immobilized laccase. Glucose is oxidized in a half-reaction at the surface of the anode electrode by the glucose oxidase to form gluconolactone, plus two hydrogen ions (protons) and two electrons. Oxygen plus four hydrogen ions and four electrons are reduced in a half-reaction at the surface of the cathode electrode by the laccase to form two water molecules. The coupled glucose oxidation-oxygen reduction half-reactions provide an efficient, stable, and self-generating current source.  
         [0022]     The nanostructured high-surface-area gold electrodes are formed on silicon or aluminum substrates to form the anode and cathode. In the first embodiment of the present invention, the electrodes are fabricated using a conventional template process in which the pores of an anodized alumina template are filled with gold by electrodeposition. The alumina template is formed by sputtering or evaporating a thin seed layer of gold followed by a layer of aluminum on a silicon, glass or aluminum substrate. The aluminum substrate is then electro-polished to remove surface defects and anodized which generates the pores and converts the aluminum to alumina. The size of the alumina template pores is controlled by adjusting the anodizing parameters, including the solution composition, operating temperature, and applied voltage.  
         [0023]     After the pores have been formed and widened by the anodizing process, gold nanowires are formed in each of the pores by conventional electrodeposition. As mentioned above, the precise number and size of the pores, and therefore the precise number of nanowires that are fabricated depends on the careful control of the anodizing parameters. Once the pores have been filled with gold via the electrodeposition process, the anodized alumina template is chemically dissolved, leaving an array of nanostructured gold electrodes bonded to the silicon, aluminum or glass substrate.  
         [0024]     The above template process results in an electrode having typical dimensions of 4 μM 2  and containing an array of approximately 1600 gold nanowires, with the exact number determined by the parameters of the anodizing process. In the first preferred embodiment fabricated according to the present invention, the estimated active reacting surface of each electrode is approximately 680 cm 2  compared to a flat surface area of 0.78 cm 2 .  
         [0025]     After the anodized alumina template is chemically dissolved, the gold nanowires and adjacent surface anode and cathode electrodes are coated with immobilized glucose oxidase and immobilized laccase, respectively, using a conventional Langmuir-Blodgett lift-off process. Using this process, one or more thin layers of immobilized enzyme are deposited onto the nanowires and adjacent surface of each electrode, resulting in the precise construction of enzyme architectures with control at the molecular level. In the present invention, the enzyme activity of both the glucose oxidase and laccase are improved using a pyrroloquinoline quinone (PQQ) mediated glucose oxidase system for the anode, with a tree-derived laccase for oxygen reduction at the cathode.  
         [0026]     In the first embodiment of the present invention, a single electrochemical cell is formed from an anode and a cathode fitted in a bio-compatible housing with a porous membrane. The porous membrane excludes macromolecules and other constituents of the plasma from the interior of the fuel cell, while being permeable to glucose, oxygen, water and ions. The glucose and water molecules are therefore able to flow into the interior of the fuel cell to react with the immobilized enzymes of the anode and cathode, respectively. The anode and cathode are separated by an insulator of, for example, silicon dioxide, thereby allowing the electrons to accumulate on the cathode and positive charges to accumulate on the anode.  
         [0027]     The amount of steady-state current generated by the electrochemical cell of the present invention is a function of the steady-state reaction rates of the oxidation and reduction processes. The reaction rates, in turn, depend primarily on the total reactive surface area of the anode and cathodes and the concentration of glucose and oxygen inside the cell. In the preferred embodiment, the total available power generated by the electrochemical cell ranges from 1000 μW to 10,000 μW.  
         [0028]     In a second embodiment of the present invention, the novel electrode structure of the electrochemical cell consists of immobilized enzyme on nanostructured high-surface-area carbon nanotube electrodes. The nanostructured high-surface-area carbon nanotube electrodes are also formed on silicon or aluminum substrates to form the anode and cathode. The electrodes are fabricated using the above anodized alumina template process, but in this case the carbon nanotubes are formed inside the pores by chemical vapor deposition.  
         [0029]     In accordance with the second embodiment of the present invention, the alumina template is again formed by sputtering or evaporating a thin seed layer of gold followed by a layer of aluminum on a silicon, glass or aluminum substrate. The aluminum substrate is then electro-polished to remove surface defects and anodized which generates the pores and converts the aluminum to alumina. As discussed in connection with the first embodiment of the present invention, the size of the alumina template pores is controlled by adjusting the anodizing parameters, including the solution composition, operating temperature, and applied voltage.  
         [0030]     After the pores have been formed and widened by the anodizing process, a thin catalyst layer of nickel, iron, or cobalt is formed in each of the pores by electrodeposition. As mentioned above, the precise number and size of the pores, and therefore the precise number of carbon nanotubes that are fabricated depends on the careful control of the anodizing parameters. Once the pores have been filled with the catalyst, carbon nanotubes are grown in each pore, again using chemical vapor deposition. After the carbon nanotubes have been formed, the anodized alumina template is chemically dissolved, leaving an array of carbon nanotubes bonded to the silicon, aluminum or glass substrate.  
         [0031]     The above template process results in an electrode having typical dimensions of 4 μM 2  and containing an array of approximately 1600 carbon nanotubes, with the exact number determined by the parameters of the anodizing process as previously described. In the second preferred embodiment fabricated according to the present invention, the estimated active reacting surface of each electrode is again approximately 680 cm 2  compared to a flat surface area of 0.78 cm 2 , with the advantage of the superior tensile strength, conductivity, chemical inertness and biocompatibility of carbon.  
         [0032]     After the anodized alumina template is chemically dissolved, the carbon nanotubes and adjacent surface anode and cathode electrodes are coated with immobilized glucose oxidase and immobilized laccase, respectively, using a conventional Langmuir-Blodgett lift-off process as described in connection with the first embodiment of the present invention.  
         [0033]     A single electrochemical cell is then fabricated from an anode and a cathode fitted in a bio-compatible housing with a porous membrane. The amount of steady-state current generated by the electrochemical cell of the second embodiment of the present invention is again a function of the steady-state reaction rates of the oxidation and reduction processes. The reaction rates, in turn, depend primarily on the total reactive surface area of the anode and cathodes and the concentration of glucose and oxygen inside the cell, both of which are the same as for the gold nanowire-based electrodes of the first embodiment described herein.  
         [0034]     A third embodiment of the present invention is similar to the first embodiment, except that the novel electrode structure consists of immobilized enzyme on nanostructured high-surface-area titanium electrodes instead of gold electrodes. The above-described electrodeposition process is used to form the titanium nanowires in a manner identical to the method used to form the gold nanowires. All of the electrical and operational properties of the third embodiment of the present invention are similar to those of the first embodiment of the present invention.  
         [0035]     In a fourth embodiment of the present invention, the nanowires or carbon nanotubes of the first, second and third embodiments, along with the adjacent surface anode and cathode electrodes are coated with spherical biocolloidal substrates containing immobilized glucose oxidase and immobilized laccase, respectively, using a modified Langmuir-Blodgett lift-off process. Using this process, one or more thin layers of biocolloidal substrates are deposited onto the nanowires or carbon nanotubes and adjacent surface of each electrode, resulting in the precise construction of an enzyme architecture with control at the molecular level, while increasing the reactive surface area by one to two orders of magnitude over the first, second, or third embodiments.  
         [0036]     As stated above in connection with the first embodiment of the present invention, the reaction rates determine the amount of power generated by the fuel cell. These rates depend primarily on the total reactive surface area of the anode and cathodes and the concentration of glucose and oxygen inside the cell. In the fourth embodiment of the present invention, the reactive surface area and the total available power generated by the electrochemical cell are both increased by one to two orders of magnitude.  
         [0037]     The first, second, third, or fourth embodiments of the present invention may also include two or more electrochemical cells connected in series to generate higher voltages.  
         [0038]     The first, second, third, or fourth embodiments of the present invention may further include two or more electrochemical cells connected in a series-parallel configuration for generating higher voltages and currents.  
         [0039]     Further features and advantages of the present invention will be appreciated by a review of the following detailed description of the preferred embodiments taken in conjunction with the following drawings. 
     
    
     BRIEF DESCRIPTION OF THE DRAWINGS  
       [0040]     The present invention may be best understood by referring to the following detailed description of the preferred embodiments and the accompanying drawings, wherein like numerals denote like elements and in which:  
         [0041]      FIG. 1A  is a first configuration of a single electrochemical cell  100  constructed in accordance with the principles of the present invention;  
         [0042]      FIG. 1B  is a second configuration of a single electrochemical cell  150  constructed in accordance with the principles of the present invention;  
         [0043]      FIGS. 2A and 2B  show the steps of a process  200  for fabricating arrays of gold or titanium nanostructured rods  106 ,  108 ,  156 , and  158 , using electrodeposition in accordance with the present invention;  
         [0044]      FIGS. 3A and 3B  show the steps of a process  300  for fabricating arrays of carbon nanotubes  106 ,  108 ,  156 , and  158 , using chemical vapor deposition in accordance with the present invention;  
         [0045]      FIG. 4  shows the steps of a first process  400  for forming the immobilized enzyme layers of the anode and cathode, in accordance with the first, second, and third embodiments of the present invention;  
         [0046]      FIGS. 5A-5C  show the steps of a second process  500  for forming immobilized enzyme layers, comprising biocolloidal substrates containing silica nanoparticles, of the anode and cathode, in accordance with the fourth embodiment of the present invention;  
         [0047]      FIG. 6  is a functional schematic  600  showing the glucose oxidation and oxygen reduction reactions of electrochemical cell  100  of the present invention;  
         [0048]      FIG. 7  is a functional schematic  700  of three electrochemical cells connected in series to provide an increased output voltage;  
         [0049]      FIG. 8  is a functional schematic  800  of six electrochemical cells connected in series parallel to provide an increased output voltage and current; and  
         [0050]      FIG. 9  is a functional schematic  900  of a complete bio-chip system with integrated power source, communicate module, sensor array, CPU control module, simulation array. 
     
    
     DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS  
       [0051]     The following exemplary discussion focuses on a bio-implantable electrochemical cell system for providing high power for active implantable medical devices. The apparatus of the present invention provides an order of magnitude improvement in power density (1,000 to 10,000 μW cm −2 ) over existing glucose/oxygen fuel cells, with a total output power of 1,000 to 10,000 μW.  
         [0052]     Referring to  FIG. 1A , a first configuration of a single electrochemical cell  100  constructed in accordance with the principles of the present invention, is shown. Electrochemical cell  100  comprises an anode  102  and a cathode  104 , both including arrays of nanostructured rods  106  and  108  in their respective interior portions. Immobile enzyme layers  110  and  112  are deposited on the interior surfaces of anode  102  and cathode  104 , respectively, including on the arrays of nanostructured rods  106  and  108 . Immobile enzyme layer  110  comprises glucose oxidase and is deposited on the interior surface and nanostructured rods of anode  102 . Immobile enzyme layer  112  comprises laccase and is deposited on the interior surface and nanostructured rods of cathode  104 .  
         [0053]     In the preferred embodiments of the present invention, the dimensions of anode  102  and cathode  104  are four microns by four microns. The dimensions of each rod of nanostructured arrays  106  and  108  are two microns in height with a diameter of 500 angstroms, with each rod being composed of gold, titanium, or carbon nanotube. The thickness of the deposited immobilized enzyme layers is approximately 200 angstroms, or less.  
         [0054]     Continuing with  FIG. 1A , anode  102  and cathode  104  are positioned within a housing  114  in a side-by-side configuration, separated by an electrically insulating material  116  such as silicon dioxide. Housing  114  is constructed from an inert bio-compatible material such as teflon, and includes a porous membrane  118  on a side opposite anode  102  and cathode  104 . Porous membrane  118  is designed to allow glucose and oxygen molecules to enter the interior of electrochemical cell  100 , and to exclude all other macromolecules.  
         [0055]     Referring now to  FIG. 1B , a second configuration of a single electrochemical cell  150 , is shown. Electrochemical cell  150  also comprises an anode  152  and a cathode  154 , both including arrays of nanostructured rods  156  and  158  in their respective interior portions. As with electrochemical cell  100 , an immobile enzyme layer  160  comprising glucose oxidase is deposited on the interior surface and nanostructured rods  156  of anode  152 , and an immobile enzyme layer  162  comprising laccase is deposited on the interior surface and nanostructured rods  158  of cathode  154 . The dimensions of anode  152  and cathode  154 , along with nanostructured rods  156  and  158 , are substantially similar to those of anode  102  and cathode  104  of electrochemical cell  100 , discussed above.  
         [0056]     In the configuration of electrochemical cell  150 , anode  152  and cathode  154  are positioned within opposite ends of a housing  164 . Housing  164  is constructed of an inert bio-compatible material such as teflon, and includes porous membranes  166  and  168  on two of its sides, opposite to each other and adjacent to anode  152  and cathode  154 . Porous membranes  166  and  168  are designed to allow glucose and oxygen molecules to enter the interior of electrochemical cell  150 , and to exclude all other macromolecules. The configuration of two porous membranes provides for an improved flow of glucose and oxygen across the arrays of nanostructured rods  156  and  158 , compared to housing  114  of electrochemical cell  100 .  
         [0057]     Continuing with  FIGS. 2A and 2B , an electrodeposition process  200  for fabricating arrays of gold or titanium nanostructured rods  106 ,  108 ,  156 , and  158  will now be disclosed. As shown in  FIGS. 2A and 2B , process  200  begins with a step  202  of evaporating or sputtering a ten nanometer thick seed layer  252  of gold on a silicon substrate  250 . Process  200  continues with a step  204  of evaporating or sputtering a two micron thick layer  254  of aluminum onto gold seed layer  252 .  
         [0058]     After layer  254  of aluminum is evaporated or sputtered onto gold seed layer  252 , electrodeposition process  200  continues with steps  206 - 210 . In step  206 , a top surface  255  of aluminum layer  254  is electropolished with perchloric-ethanol and H 3 PO 4 -butanol to remove any surface defects. In step  208 , aluminum layer  254  is anodized using H 2 SO 4 , H 3 PO 4 , mixed H 2 SO 4 /H 3 PO 4 , and oxalic acid. Anodizing step  208  converts aluminum layer  254  to porous alumina, whereby approximately 1,600 pores are produced during step  208 . In step  210 , the pores of alumina layer  254  are widened to an average approximate diameter of 500 angstroms using 0.2 M of H 3 PO 4  which completes the anodizing process.  
         [0059]     Continuing now with  FIGS. 2A and 2B , electrodeposition process  200  continues with a step  212  of electrodepositing gold or titanium into the pores of alumina layer  254 . Process  200  continues with a step  214  of dissolving alumina layer  254  by chemical etching, leaving the approximately 1,600 gold or titanium nanostructured rods attached to silicon substrate  250 . As mentioned above, each nanostructured rod is approximately two microns in height and 500 angstroms in diameter.  
         [0060]     Referring now to  FIGS. 3A and 3B , a chemical vapor deposition process  300  for fabricating arrays of carbon nanotube rods  106 ,  108 ,  156 , and  158  will now be disclosed. As shown in  FIGS. 3A and 3B , process  300  begins with a step  302  of evaporating or sputtering a ten nanometer thick seed layer  352  of gold on a silicon substrate  350 . Process  300  continues with a step  304  of evaporating or sputtering a two micron thick layer  354  of aluminum onto gold seed layer  352 .  
         [0061]     After layer  354  of aluminum is evaporated or sputtered onto gold seed layer  352 , a chemical vapor deposition process  300  continues with steps  306 - 310 . In step  306 , a top surface  355  of aluminum layer  354  is electropolished with perchloricethanol and H 3 PO 4 -butanol to remove any surface defects. In step  308 , aluminum layer  354  is anodized using H 2 SO 4 , H 3 PO 4 , mixed H 2 SO 4 /H 3 PO 4 , and oxalic acid. Anodizing step  308  converts aluminum layer  354  to porous alumina, whereby approximately 1,600 pores are produced during step  308 . In step  310 , the pores of alumina layer  354  are widened to an average approximate diameter of 500 angstroms using 0.2 M of H 3 PO 4  which completes the anodizing process.  
         [0062]     Continuing now with  FIGS. 3A and 3B , chemical vapor deposition process  300  continues with a step  312  of a catalyst layer of iron (Fe), cobalt (Co), or nickel (Ni) into the pores of alumina layer  354 , followed by a step  314  of growing carbon nanotubes at 700° C. Process  300  continues with a step  316  of dissolving alumina later  354  by chemical etching, leaving the approximately 1,600 carbon nanotubes attached to silicon substrate  350 . As mentioned above, each carbon nanotube is approximately two microns in height and 500 angstroms in diameter.  
         [0063]     Continuing with  FIG. 4 , the steps of a first process  400  for forming and depositing immobilized enzyme layers  110 ,  112 ,  160 , and  162  on anodes  102  and  152 , and cathodes  104  and  154 , in accordance with the first, second, and third embodiments of the present invention, are now disclosed. Process  400  is based on a conventional Langmuir-Blodgett process (See: Langmuir-Blodgett Films, edited by G. Roberts, Plenum, New York, 1990) for depositing monolayer organic films on a solid substrate that provides: (1) precise control of the monolayer thickness; (2) homogeneous deposition of the monolayer over large areas; and (3) the ability to build multi-layer structures with varying layer composition. An additional advantage of the Langmuir-Blodgett technique is that monolayers can be deposited on almost any type of substrate.  
         [0064]     The Langmuir-Blodgett technique uses the surface free energy and surface tension properties of a liquid at the gas/liquid interface. In the particular case of a polar liquid such as water, there are strong intermolecular interactions and thus high surface tension. Any factor which decreases the strength of these interactions, especially the presence of surface active agents (surfactants), will lower the surface tension of the liquid.  
         [0065]     Surfactants are amphiphilic molecules that consist of a hydrophilic (water soluble) and a hydrophobic (water insoluble) part. The hydrophilic part usually consists of a polar group and the hydrophobic part consists of hydrocarbon or fluorocarbon chains. The hydrocarbon or fluorocarbon chain has to be long enough to form an insoluble monolayer; otherwise, the amphiphiles on the water surface tend to form water soluble micelles that prevent build up of a monolayer. However, if the chain is too long the amphiphile tends to crystallize on the water surface, which again prevents the build up of a monolayer. Fortunately, a wide range of amphiphiles exist which lower the surface tension of water, and the amphiphilic nature of the molecules dictates the orientation of the molecules at the air/water interface.  
         [0066]     When a solution of an amphipile in a water soluble solvent is placed on a water surface, the solution spreads rapidly to cover the available area. As the solvent evaporates, a monolayer is formed on the surface of the water. When the available area for the monolayer is large, the distance between adjacent amphiphilic molecules is large and their interactions are weak. This is referred to as the “gas phase” and in this phase the monolayer has very little effect on the surface tension of the water.  
         [0067]     However, if the available surface area of the monolayer is reduced by a barrier system, the amphiphilic molecules begin to exert a repulsive force on each other and the monolayer transitions from the gas to a “liquid phase.” If the area is reduced further, the monolayer will eventually transition from the liquid to a “solid phase” in which the Langmuir-Blodgett technique is carried out. In the solid phase, the surface pressure is sufficiently high to ensure that the attraction between the monolayer molecules is high enough so that the monolayer does not fall apart during transfer to the solid substrate. This also ensures the build up of homogeneous multi-layers.  
         [0068]     Note that the phase behavior of a specific amphiphile is determined by its physical and chemical properties, including temperature, the length of the hydrocarbon chain, and the magnitude of other cohesive and repulsive forces existing between the polar groups.  
         [0069]     Referring again to  FIG. 4 , process  400  begins with a step  402  of depositing a solution containing one of immobile enzymes  110 ,  112  (glucose oxidase) or  160 ,  162  (laccase) on the surface of water contained in a teflon trough (not shown). The surface area of the water of controlled to maintain the monolayer in the solid phase by a pair of sweeping movable barriers (not shown) made of a hydrophilic material such as Delrin. Process  400  continues with a step  404  of successively dipping and withdrawing anodes  102  and  152 , and cathodes  104  and  154  up and down through the enzyme monolayer while simultaneously maintaining a constant surface pressure by a computer-controlled feedback system. Since gold, titanium and carbon are hydrophobic, the first enzyme monolayer is deposited by lowering the anode or cathode into the water through the monolayer. As shown in  FIG. 4 , the first enzyme monolayer is adsorbed with the hydrocarbon chains toward the surface of anodes  102  and  152 , and cathodes  104  and  154  in the down direction. Subsequent layers are formed by deposits in both the up and down directions, and in this way multi-layered structures of immobile enzymes  110 ,  112 ,  160 , or  162  are produced.  
         [0070]      FIGS. 5A-5C  show the exemplary steps of a second process  500  for forming and depositing immobilized enzyme layers  110 ,  112 ,  160 , or  162  containing latex or other biocolloidal substrates and silica nanoparticles, on the surfaces and nanostructured rods of anodes  102  and  152 , and cathodes  104  and  154 . Process  500  begins with steps  502 - 528  of forming biocolloidal substrates containing silica nanoparticles and immobilized enzymes  110 ,  112  (glucose oxidase) or  160 ,  162  (laccase), using a modified layer-by-layer assembly process (See: M. Fang, P. Grant, M. McShane, G. Sukhorukov, V. Golub, Y. Lvov, Langmuir, 2002, v. 18, 6338-6344. “Magnetic Bio/Nanoreactor with Multilayer Shells of Glucose Oxidase and Inorganic Nanoparticles”). Steps  502 - 528  involve the stepwise growth of organized layers of oppositely charged polyelectrolytes, silica, and immobilized enzyme layers on biocolloidal substrates; for example, on latex spheres or carbon buckyballs, by alternately processing the substrates in polycation (positively charged) and polyanion (negatively charged) solutions. The inclusion of the silica layers yields a higher substrate surface area, resulting in greater enzyme adsorption and thereby increasing the catalytic activity of the immobilized enzyme. The deposition mechanisms in this process are electrostatic attraction, van der Waal forces, and capillary forces.  
         [0071]     Continuing with  FIG. 5A , steps  502 - 514  describing the formation of biocolloidal substrates containing organized layers of silica nanoparticles and glucose oxidase, are now described. Beginning with step  502 , a first polycationic solution is added to a suspension of biocolloidal substrates until adsorption saturation. Biocolloidal substrates may comprise latex spheres or carbon buckyballs. In step  504 , a polyanionic solution is added to the suspension of biocolloidal substrates until adsorption saturation. Steps  502  and  504  are performed twice. In step  506 , a second polycationic solution is added to the suspension of biocolloidal substrates until adsorption saturation. In step  508 , silica nanoparticles are added to the suspension of biocolloidal substrates until adsorption saturation. Steps  506  and  508  are performed one to four times. In step  510 , a third polycationic solution is added to the suspension of biocolloidal substrates until adsorption saturation. In step  512 , a polyanionic solution containing glucose oxidase is added to the suspension of biocolloidal substrates until adsorption saturation occurs. Steps  510 - 512  are performed once or twice. After each of steps  502 - 512 , in a step  514  the coated biocolloidal substrates are separated from the unabsorbed species by centrifugation and the supernatant containing the unabsorbed species is removed. At this stage, the biocolloidal substrates are coated with up to four layers of silica nanoparticles and one or two layers of immobilized glucose oxidase with the following shell architectures: 
 
{PEI/PSS} 2 +{PEI/silica} 0-4 +{PEI/GO x } 1-2 . 
 
 where PEI is polyethyleneimine, PSS is polystyrenesulfonate. 
 
         [0072]     Referring to  FIG. 5B , steps  516 - 528  are now used to describe the formation of biocolloidal substrates containing organized layers of silica nanoparticles and laccase. In this case, the differences are the reversals of the polycationic and polyanionic solutions, and the substitution of laccase in place of glucose oxidase.  
         [0073]     Beginning with step  516 , a first polyanionic solution is added to a suspension of biocolloidal substrates until adsorption saturation. In step  518 , a polycationic solution is added to the suspension of biocolloidal substrates until adsorption saturation. Steps  516  and  518  are performed twice. In step  520 , a second polyanionic solution is added to the suspension of biocolloidal substrates until adsorption saturation. In step  522 , silica nanoparticles are added to the suspension of biocolloidal substrates until adsorption saturation. Steps  520  and  522  are performed one to four times. In a step  524 , a third polyanionic solution is added to the suspension of biocolloidal substrates until adsorption saturation. In step  526 , a polycationic solution containing laccase is added to the suspension of biocolloidal substrates until adsorption saturation occurs. Steps  524  and  526  are performed one or two times. After each of steps  516 - 526 , in a step  528  the biocolloidal substrates are separated from the unabsorbed species by centrifugation and the supernatant containing the unabsorbed species is removed. At this stage, the biocolloidal substrates are coated with up to four layers of silica nanoparticles and one or two layers of immobilized laccase with the following shell architectures: 
 
{PSS/PEI} 2 +{PSS/silica} 0-4 +{PSS/laccase} 12 . 
 
         [0074]     Referring now to  FIG. 5C , process  500  continues with a step  530  of depositing a solution, containing the biocolloidal substrates coated with silica nanoparticles and one of immobile enzymes  110 ,  112  or  160 ,  162 , on the surface of water contained in a teflon trough (not shown). The surface area of the water of controlled to maintain the monolayer in the solid phase by a pair of sweeping movable barriers (not shown) made of a hydrophilic material such as Delrin. Process  500  continues with a step  532  of successively dipping and withdrawing anodes  102  and  152 , and cathodes  104  and  154  up and down through the biocolloidal substrate monolayer while simultaneously maintaining a constant surface pressure by a computer-controlled feedback system. As discussed in connection with  FIG. 4  and process  400 , since gold, titanium and carbon are hydrophobic, the first biocolloidal substrate monolayer is deposited by lowering the anode or cathode into the water through the monolayer.  
         [0075]     Referring now to  FIG. 6 , the glucose oxidation and oxygen reduction reactions of electrochemical cells  100  and  150  of the present invention, are now disclosed. A unit cell of this bio-fuel cell consists of two compartments  602  and  604 . Individual compartment is made up of a porous membrane top layer  606 , bio-compatible material coated side-walls  608 , and a nanowire-based bottom layer  610  on a heavily-doped silicon substrate  612 . A heavily-doped silicon substrate also has a number of pores  614  with a few hundred nanometer-size diameter. The nanowire-based cathode electrodes  616  and anode electrodes  618  are coated with glucose oxidase (GOx) enzymes  620  and laccase enzymes  622 , respectively. Individual substrate  612  and  624  plays a role of conducting paths for electrons from nanowire-based cathodes  616  and anodes  610  to outside world  626  and  628 , respectively. The back-side of substrates containing nanowire-based cathode  616  and anode  610  compartments are bonded together having an insulator layer  630  in between so glucose is diffused into the cell from both the top-porous membrane and the bottom-porous membrane. GOx-catalyzed oxidation of glucose at the anode is coupled with laccase-catalyzed oxygen reduction at the cathode in a miniature, non-compartmentalized system.  
         [0076]     In electrochemical cells  100  and  150 , glucose is oxidized by glucose oxidase (GO x ) in a half-reaction at anode  610  or  152 , respectively. Simultaneously, oxygen is reduced by laccase in a half-reaction at cathode  616  or  154 , respectively. The following are the combined half-reactions: 
 
Glucose→gluconolactone+2H + +2e − : cathode O 2 +4H + +4e − →2H 2 O: anode 
 
         [0077]     More specifically, glucose oxidase catalyzes the oxidation of each molecule of β-D-glucose to D-gluconic acid and hydrogen peroxide. Since glucose oxidase is highly specific for β-D-glucose, it does not act on α-D-glucose; however, as a result of the consumption of β-D-glucose, α-D-glucose is converted into the β-form by mutarotation. The two electrons that are released by each glucose molecule from the nanowire-based cathode generating gluconolactone are used to perform electrical work through an external circuit.  
         [0078]     Once the two electrons released by glucose oxidation with each glucose molecule have performed electrical work, laccase catalyzes the reduction of an oxygen molecule, four hydrogen nuclei and four electrons to form two water molecules. Laccase is a copper-containing phenyloxidase that requires a pH of 5.0 for optimal activity and stability; however, the pH of the human body is normally 7.2-7.4 so an effective system that operates at neutral pH is needed. This is accomplished in the present invention by using a pyrroloquinoline quinone (PQQ) mediated glucose oxidase system with tree-derived laccase.  
         [0079]     A related issue is eliminating the need for membrane-separated anode and cathode compartments. In the present invention, this need is eliminated through effective coupling of the immobilized enzymes to the anode and cathode, so that very little glucose reacts at the cathode, and very little oxygen reacts at the anode.  
         [0080]     Continuing with  FIGS. 7 and 8 , functional schematics of three electrochemical cells connected in series  700  to provide an increase output voltage, and six electrochemical cells connected in series-parallel  800 , are disclosed. As exemplified in  FIG. 7 , any number of cells may be connected in series to generate sufficient voltage to power active implanted medical devices. Similarly, as exemplified in  FIG. 8 , any number of cells may be connected in series-parallel to provide for the generation of sufficient voltage and current to power any type of active implantable medical device.  
         [0081]     Referring now to  FIG. 9 , a functional schematic of an integrated implantable medical device  900  will now be discussed. Device  900  is an example of the type of single-chip, programmable devices that are possible using the electrochemical cell of the present invention, and may comprise a substrate  902  on which are fabricated a power source  904 , a sensor array  906 , a CPU/control module  908 , a stimulation array  910 , and a communication module  912 .  
         [0082]     For example, in one embodiment, device  900  may be programmed to function as a rate-adaptive cardiac pacemaker, in which sensor array  906  is configured to measure one or more parameters related to the physiologically correct value of the cardiac stimulation frequency. Such measured parameters may, for example, relate respiration with circulation activity to determine the physiologically correct stimulation frequency. CPU/control module  908  is programmed to establish the physiologically correct rate of the stimulation pulses, depending on the measured physiological parameters. Stimulation array  910  is then configured to generate stimulation pulses to the heart. Communication module  912  is configured to store and output calibration and control parameters to a receiver located external to the body.  
         [0083]     Because device  900  includes electrochemical power source  904  and communication module  912  integrated on a common substrate  902 , the device may be much smaller than existing implantable devices. In addition, since power source  904  does not require recharging, device  900  may be implanted essentially permanently.  
         [0084]     The foregoing description includes what are at present considered to be preferred embodiments of the present invention. However, it will be readily apparent to those skilled in the art that various changes and modifications may be made to the embodiments without departing from the spirit and scope of the invention. For example, the exact dimensions of the electrochemical cell, the nanowires, or the carbon nanotubes may be changed. Alternatively, the precise dimensions, quantity, and composition of the biocolloidal substrates that are affixed to the anode and cathode may vary. Accordingly, it is intended that such changes and modifications fall within the spirit and scope of the invention, and that the present invention be limited only by the following claims.

Technology Classification (CPC): 7