Abstract:
In a method of fabricating a microstructure for microfluidics applications, a first layer of etchable material is formed on a suitable substrate. A mechanically stable support layer is formed over the etchable material. A mask is applied over the support to expose at least one opening in the mask. An anistropic etch is then performed through the opening to create a bore extending through the support layer to said layer of etchable material. After performing an isotropic etch through the bore to form a microchannel in the etchable material extending under the support layer, a further layer is deposited over the support layer until overhanging portions meet and thereby close the microchannel formed under the opening.

Description:
BACKGROUND OF THE INVENTION 
     1. Field of the Invention 
     This invention relates to the field of integrated device fabrication, and more particularly to the manufacture of integrated devices for use in microfluidics applications, such biological applications; in the latter case such devices are often known as biochips. Biochips require the fabrication of micro-channels for the processing of biological fluids, and the present invention relates a method of fabricating such channels. 
     2. Description of the Prior Art 
     The prior art is generally divided into two types of device: Passive and Active. Both types include microchannels for the transport of biological fluids. In passive devices all the control circuitry for fluid flow is on external circuitry. Active devices include control circuitry incorporated directly into the biochip. 
     The following granted U.S.A. Patents show the Prior Art concerning the fabrication of micro-channel biochips for the processing of biological fluids: U.S. Pat. No. 6,186,660, “Microfluidic systems incorporating varied channel dimensions”; U.S. Pat. No. 6,180,536, “Suspended moving channels and channel actuators for . . . ”; U.S. Pat. No. 6,174,675, “Electrical current for controlling fluid parameters in . . . ”; U.S. Pat. No. 6,172,353, “System and method for measuring low power signals”; U.S. Pat. No. 6,171,865, “Simultaneous analyte determination and reference balancing . . . ; U.S. Pat. No. 6,171,850, “Integrated devices and systems for performing temperature . . . ”; U.S. Pat. No. 6,171,067, “Micropump”; U.S. Pat. No. 6,170,981, “In situ micromachined mixer for microfluidic analytical . . . ”; U.S. Pat. No. 6,167,910, “Multi-layer microfluidic devices”; U.S. Pat. No. 6,159,739, “Device and method for 3-dimensional alignment of particles . . . ”; U.S. Pat. No. 6,156,181, “Controlled fluid transport microfabricated polymeric substrates”; U.S. Pat. No. 6,154,226, “Parallel print array”; U.S. patent No. substrates”; U.S. Pat. No. 6,154,226, “Parallel print array”; U.S. Pat. No. 6,153,073, “Microfluidic devices incorporating improved channel . . . ”; U.S. Pat. No. 6,150,180, “High throughput screening assay systems in microscale . . . ”; U.S. Pat. No. 6,150,119, “Optimized high-throughput analytical system ”; U.S. Pat. No. 6,149,870, “Apparatus for in situ concentration and/or dilution of . . . ”; U.S. Pat. No. 6,149,787, “External material accession systems and methods”; U.S. Pat. No. 6,148,508, “Method of making a capillary for electrokinetic transport of . . . ”; U.S. Pat. No. 6,146,103, “Micromachined magnetohydrodynamic actuators and sensors ”; U.S. Pat. No. 6,143,248, “Capillary microvalve”; U.S. Pat. No. 6,143,152, “Microfabricated capillary array electrophoresis device and . . . ”; U.S. Pat. No. 6,137,501, “Addressing circuitry for microfluidic printing apparatus”; U.S. Pat. No. 6,136,272, “Device for rapidly joining and splitting fluid layers”; U.S. Pat. No. 6,136,212, “Polymer-based micromachining for microfluidic devices”; U.S. Pat. No. 6,132,685, “High throughput microfluidic systems and methods”; U.S. Pat. No. 6,131,410, “Vacuum fusion bonding of glass plates”; U.S. Pat. No. 6,130,098, “Moving microdroplets”; U.S. Pat. No. 6,129,854, “Low temperature material bonding technique”; U.S. Pat. No. 6,129,826, “Methods and systems for enhanced fluid transport”; U.S. Pat. No. 6,126,765, “Method of producing microchannel/microcavity structures”; U.S. Pat. No. 6,126,140, “Monolithic bi-directional microvalve with enclosed drive . . . ”; U.S. Pat. No. 6,123,798, “Methods of fabricating polymeric structures incorporating . . . ”; U.S. Pat. No. 6,120,666, “Microfabricated device and method for multiplexed . . . ”; U.S. Pat. No. 6,118,126, “Method for enhancing fluorescence”; U.S. Pat. No. 6,107,044, “Apparatus and methods for sequencing nucleic acids in . . . ”; U.S. Pat. No. 6,106,685, “Electrode combinations for pumping fluids”; U.S. Pat. No. 6,103,199, “Capillary electroflow apparatus and method”; U.S. Pat. No. 6,100,541, “Microfluidic devices and systems incorporating integrated . . . ”; U.S. Pat. No. 6,096,656, “Formation of microchannels from low-temperature . . . ”; U.S. Pat. No. 6,091,502, “Device and method for performing spectral measurements in . . . ”; U.S. Pat. No. 6,090,251, “Microfabricated structures for facilitating fluid introduction . . . ”; U.S. Pat. No. 6,086,825, “Microfabricated structures for facilitating fluid introduction . . . ”; U.S. Pat. No. 6,086,740. “Multiplexed microfluidic devices and systems”; U.S. Pat. No. 6,082,140, “Fusion bonding and alignment fixture ”; U.S. Pat. No. 6,080,295, “Electropipettor and compensation means for electrophoretic . . . ”; U.S. Pat. No. 6,078,340, “Using silver salts and reducing reagents in microfluidic printing”; U.S. Pat. No. 6,074,827, “Microfluidic method for nucleic acid purification and processing”; U.S. Pat. No. 6,074,725, “Fabrication of microfluidic circuits by printing techniques”; U.S. Pat. No. 6,073,482, “Fluid flow module”; U.S. Pat. No. 6,071,478, “Analytical system and method”; U.S. Pat. No. 6,068,752, “Microfluidic devices incorporating improved channel . . . ”; U.S. Pat. No. 6,063,589, “Devices and methods for using centripetal acceleration to . . . ”; U.S. Pat. No. 6,062,261, “MicrofluIdic circuit designs for performing electrokinetic . . . ”; U.S. Pat. No. 6,057,149, “Microscale devices and reactions in microscale devices”; U.S. Pat. No. 6,056,269, “Microminiature valve having silicon diaphragm”; U.S. Pat. No. 6,054,277, “Integrated microchip genetic testing system”; U.S. Pat. No. 6,048,734, “Thermal microvalves in a fluid flow method”; U.S. Pat. No. 6,048,498, “Microfluidic devices and systems”; U.S. Pat. No. 6,046,056, “High throughput screening assay systems in microscale . . . ”; U.S. Pat. No. 6,043,080, “Integrated nucleic acid diagnostic device ”; U.S. Pat. No. 6,042,710, “Methods and compositions for performing molecular separations”; U.S. Pat. No. 6,042,709, “Microfluidic sampling system and methods”; U.S. Pat. No. 6,012,902, “Micropump”; U.S. Pat. No. 6,011,252, “Method and apparatus for detecting low light levels”; U.S. Pat. No. 6,007,775, “Multiple analyte diffusion based chemical sensor”; U.S. Pat. No. 6,004,515, “Methods and apparatus for in situ concentration and/or . . . ”; U.S. Pat. No. 6,001,231, “Methods and systems for monitoring and controlling fluid . . . ”; U.S. Pat. No. 5,992,820, “Flow control in microfluidics devices by controlled bubble . . . ”; U.S. Pat. No. 5,989,402, “Controller/detector interfaces for microfluidic systems”; U.S. Pat. No. 5,980,719, “Electrohydrodynamic receptor”; U.S. Pat. No. 5,972,710, “Microfabricated diffusion-based chemical sensor”; U.S. Pat. No. 5,972,187, “Electropipettor and compensation means for electrophoretic bias”; U.S. Pat. No. 5,965,410, “Electrical current for controlling fluid parameters in . . . ”; U.S. Pat. No. 5,965,001, “Variable control of electroosmotic and/or electrophoretic . . . ”; U.S. Pat. No. 5,964,995, “Methods and systems for enhanced fluid transport”; U.S. Pat. No. 5,958,694, “Apparatus and methods for sequencing nucleic acids in . . . ”; U.S. Pat. No. 5,958,203, “Electropipettor and compensation means for electrophoretic bias”; U.S. Pat. No. 5,957,579, “Microfluidic systems incorporating varied channel dimensions”; U.S. Pat. No. 5,955,028, “Analytical system and method”; U.S. Pat. No. 5,948,684, “Simultaneous analyte determination and reference balancing . . . ”; U.S. Pat. No. 5,948,227, “Methods and systems for performing electrophoretic . . . ”; U.S. Pat. No. 5,942,443, “High throughput screening assay systems in microscale”; U.S. Pat. No. 5,932,315, “Microfluidic structure assembly with mating microfeatures”; U.S. Pat. No. 5,932,100, “Microfabricated differential extraction device and method . . . ”; U.S. Pat. No. 5,922,604, “Thin reaction chambers for containing and handling liquid . . . ”; U.S. Pat. No. 5,922,210, “Tangential flow planar microfabricated fluid filter and method . . . ”; U.S. Pat. No. 5,885,470, “Controlled fluid transport in microfabricated polymeric . . . ”; U.S. Pat. No. 5,882,465, “Method of manufacturing microfluidic devices”; U.S. Pat. No. 5,880,071, “Electropipettor and compensation means for electrophoretic bias”; U.S. Pat. No. 5,876,675, “Microfluidic devices and systems”; U.S. Pat. No. 5,869,004, “Methods and apparatus for in situ concentration and/or . . . ”; U.S. Pat. No. 5,863,502, “Parallel reaction cassette and associated devices”; U.S. Pat. No. 5,856,174, “Integrated nucleic acid diagnostic device”; U.S. Pat. No. 5,855,801, “IC-processed microneedles”; U.S. Pat. No. 5,852,495, “Fourier detection of species migrating in a microchannel”; U.S. Pat. No. 5,849,208, “Making apparatus for conducting biochemical analyses”; U.S. Pat. No. 5,842,787, “Microfluidic systems incorporating varied channel dimensions”; U.S. Pat. No. 5,800,690, “Variable control of electroosmotic and/or electrophoretic . . . ”; U.S. Pat. No. 5,779,868, “Electropipettor and compensation means for electrophoretic bias”; U.S. Pat. No. 5,755,942, “Partitioned microelectronic device array”; U.S. Pat. No. 5,716,852, “Microfabricated diffusion-based chemical sensor”; U.S. Pat. No. 5,705,018, “Micromachined peristaltic pump”; U.S. Pat. No. 5,699,157, “Fourier detection of species migrating in a microchannel”; U.S. Pat. No. 5,591,139, ““IC-processed microneedles”; and U.S. Pat. No. 5,376,252, “Microfluidic structure and process for its manufacture”. 
     The following published paper describes a polydimethylsiloxane (PDMS) biochip capable of capacitance detection of biological entities (mouse cells): L. L. Sohn, O. A. Saleh, G. R. Facer, A. J. Beavis, R. S. Allan, and D. A. Notterman, ‘Capacitance cytometry: Measuring biological cells one by one’, Proceedings of the National Academy of Siences (USA), Vol. 97, No. 20, Sep. 26, 2000, pp.10687-10690 
     The above US patents indicate that passive micro-channel biochip devices are largely fabricated from the combination of various polymer substrates, such as: acrylonitrile-butadiene-styrene copolymer, polycarbonate, polydimethylsiloxane (PDMS), polyethylene, polymethylmethacrylate (PMMA), polymethylpentene, polypropylene, polystyrene, polysulfone, polytetrafluoroethylene (PTFE), polyurethane, polyvinylchloride (PVC), polyvinylidine fluoride (PVF), or other polymer. In this case, lithography or mechanical stamping is used to define a network of micro-channels in one of these substrates, prior to the assembly and the thermally assisted bonding of this first substrate to another substrate. The result is a simple passive micro-channel biochip device which can be patterned with conductive layers for connection to an external processor that is used to initiate fluid movement by electrophoresis or electroosmosis, and for analysis and data generation. FIG. 1 shows an example of such a passive micro-channel biochip device obtained from the fusion of such polymeric substrates described in U.S. Pat. No. 6,167,910. 
     The prior art US patents also show that passive micro-channel biochip devices can be fabricated from the combination of various micro-machined silica or quartz substrates. Again, assembly and fusion bonding is required. The result is a simple passive biochip device which can be patterned with conductive layers for connection to an external processor. FIG. 2 shows an example of such passive micro-channel biochip device obtained from the fusion of such silica substrates as described in U.S. Pat. No. 6,131,410. 
     These prior art patents also show that passive micro-channel biochip devices can be fabricated from a passive micro-machined silicon substrate. In that case, the silicon substrate is used as a passive structural material. Again, assembly and fusion bonding of at least two sub-assemblies is required. The result is a simple passive biochip that has to be connected to an external processor. FIG. 3 shows an example of such a passive micro-channel biochip devices obtained from a passive micro-machined silicon substrate in accordance with the teachings of U.S. Pat. No. 5,705,018. 
     The prior patents also indicate that an active micro-reservoir biochip device can be fabricated from an active micro-machined silicon substrate. In this case, the control electronics integrated in the silicon substrate is used as an active on-chip fluid processor and communication device. The result is a sophisticated biochip which can perform, in pre-defined reservoirs, various fluidic operations, analysis and (remote) data communication functions without the need for an external fluid processor controlling fluid movement, analysis and data generation. FIG. 4 shows an example of an active micro-reservoir biochip devices obtained from an active micro-machined silicon substrate described in U.S. Pat. No. 6,117,643. 
     The published paper discloses that capacitance detection of biological entities can be performed on passive polydimethylsiloxane (PDMS) biochips using gold coated capacitor electrodes at a relatively low frequency of 1 kHz with and external detector. FIG. 5 shows an example of such passive polydimethylsiloxane (PDMS) biochips with gold electrodes. 
     SUMMARY OF THE INVENTION 
     The present invention relates to an improved fabrication technique of active micro-channel biochip devices from an active micro-machined silicon substrate that results in a sophisticated biochip device which can perform fluid movement and biological entities detection into micro-channels. 
     According to the present invention there is provided a method of fabricating a microstructure for microfluidics applications, comprising forming a layer of etchable material on a suitable substrate; forming a mechanically stable support layer over said etchable material; applying a mask over said support layer to expose at least one opening; performing an anistropic etch through the or each said opening to create a bore extending through said support layer into said layer of etchable material; performing an isotropic etch through the or each said bore to form a microchannel in said etchable material extending under said support layer; and forming a further layer of depositable material over said support layer until portions of said depositable layer overhanging the or each said opening meet and thereby close the microchannel formed under the or each said opening. 
     The invention involves the formation of a structure comprising a stack of layers. It will be appreciated by one skilled in the art that the critical layers do not necessarily have to be deposited directly on top of each other. It is possible that in certain applications intervenving layers may be present, and indeed in the preferred embodiment such layers, for example, a sacrificial TiN layer, are present under the support layer. 
     The invention offers a simple approach for the fabrication of active micro-channel biochip devices from an active micro-machined silicon substrate directly over a Complementary Metal Oxide Semiconductor device, CMOS device, or a high-voltage CMOS device. 
     CMOS devices are capable of very small detection levels, an important prerequisite in order to perform electronic capacitance detection (identification) of biological entities with low signal levels. CMOS devices can perform the required data processing and (remote) communication fonctions. High-voltage CMOS devices with adequate operation voltages and operation currents are capable of performing the required micro-fluidics in the micro-channels and allowing the integration of a complete Laboratory-On-A-Chip concept. 
     The invention discloses a technique for incorporating in existing CMOS and high-voltage CMOS processes the micro-machining steps which allow the development of the active micro-channels with attached electrodes used to provoke fluid movement and/or to identify biological entities. The micro-channels are closed using without the use of a second substrate and without the use of thermal bonding. In fact, all of the described micro-machining steps should preferably be carried out at a temperature not exceeding 450° C. in order to prevent the degradation of the underlying CMOS and high-voltage CMOS devices and, prevent any mechanical problems such as plastic deformation, peeling, cracking, de-lamination and other such high temperature related problems with the thin layers used in the micro-machining of the bio-chip. 
     The materials combination used in the described micro-machining sequence are not typical of Micro-Electro-Mechanical-Systems (MEMS) which typically use Low Pressure Chemical Vapour Deposited polysilicon, LPCVD polysilicon, and Plasma Enhanced Chemical Vapour Deposited silica, PECVD SiO 2 , combinations. The use of LPCVD polysilicon is generally not suitable because of its required deposition temperature of more than 550° C. 
     The invention preferably employs as an innovative sacrificial material Collimated Reactive Physical Vapour Deposition of Titanium Nitride, CRPVD TiN. In this process the TiN is deposited with the assistance of a collimator, which directs the atoms onto the supporting surface. This sacrificial CRPVD TiN material is used because of its excellent mechanical properties, and its excellent selectivity to Isotropic Wet Etching solutions used to define the micro-channels in thick layers of Plasma Enhanced Chemical Vapour Deposited, PECVD, SiO 2 . 
     Typically, the capacitor electrodes are either LPCVD polysilicon (deposited before the micro-machining steps) or Physical Vapour Deposited aluminum alloy, PVD Al-alloy. 
    
    
     BRIEF DESCRIPTION OF THE DRAWINGS 
     The invention will now be described in more detail, by way of example only, with reference to the accompanying drawings, in which: 
     FIG. 1 shows one example of a passive micro-channel biochip device obtained from the fusion of polymeric substrates as described in U.S. Pat. No. 6,167,910; 
     FIG. 2 shows one example of a passive micro-channel biochip device obtained from the fusion of silica substrates as described in U.S. Pat. No. 6,131,410; 
     FIG. 3 shows one example of a passive micro-channel biochip device obtained from a passive micro-machined silicon substrate as described in U.S. Pat. No. 5,705,018; 
     FIG. 4 shows one example of an active micro-reservoir biochip device obtained from an active micro-machined silicon substrate as descried in U.S. Pat. No. 6,117,643; 
     FIG. 5 shows one example of a passive polydimethylsiloxane (PDMS) biochip with gold electrodes as described in the article by L. L. Sohn, O. A. Saleh, G. R. Facer, A. J. Beavis, R. S. Allan, and D. A. Notterman, entitled ‘Capacitance cytometry: Measuring biological cells one by one’, Proceedings of the National Academy of Siences (USA), Vol. 97, No. 20, Sep. 26, 2000, pp.10687-10690); 
     FIG. 6 illustrates step  1  of a biochip micro-machining sequence (Deposition of 0.1 μm of PECVD Si 3 N 4  at 400° C.); 
     FIG. 7 illustrates steps  2  to  6  of the biochip micro-machining sequence (Deposition of 0.10 μm of CRPVD TiN at 400° C., Deposition of 10.0 μm of PECVD SiO 2  at 400° C., Deposition of 0.10 μm of CRPVD TiN at 400° C., Deposition of 0.40 μm of PECVD Si 3 N 4  at 400° C., Deposition of 0.20 μm of CRPVD TiN at 400° C.); 
     FIG. 8 illustrates step  7  of the biochip micro-machining sequence (1st Pattern Followed by Partial Anisotropic Reactive Ion Etch-back); 
     FIG. 9 illustrates step  8  of the biochip micro-machining sequence (2nd Pattern Followed by Anisotropic Reactive Ion Etch-back and Etch Holes); 
     FIG. 10 illustrates step  9  of the biochip micro-machining sequence (Deposition of 0.10 μm of CRPVD TiN at 400° C.); 
     FIG. 11 illustrates step  10  of the biochip micro-machining sequence (Anisotropic Reactive Ion Etch-back of 0.10 μm of CRPVD TiN); 
     FIG. 12 illustrates step  11  of the biochip micro-machining sequence (Controlled Isotropic Wet Etching of the PECVD SiO 2 ); 
     FIG. 13 illustrates step  12  of the biochip micro-machining sequence (Isotropic Wet Removal of Exposed CRPVD TiN with Some Undercut); 
     FIG. 14 illustrates step  13  of the biochip micro-machining sequence (Deposition of 1.40 μm of PECVD SiO 2  at 400° C.); 
     FIG. 15 illustrates step  14  of the biochip micro-machining sequence (3rd Pattern and Isotropic Wet Etching of the PECVD SiO 2  at 400° C.); 
     FIG. 16 illustrates step  15  of the biochip micro-machining sequence (Standard Deposition of PVD Ti/CRPVD TiN/PVD Al-alloy/CRPVD TiN at 400° C.); 
     FIG. 17 illustrates step  16  of the biochip micro-machining sequence (Standard Anisotropic RIE of PVD Ti/CRPVD TiN/PVD Al-alloy/CRPVD TiN); 
     FIG. 18 shows scanning Electron Micrograph, SEM, cross sectional views demonstrating the excellent mechanical stability of a TiN layer to be suspended over the micro-channel; 
     FIG. 19 is a Scanning Electron Micrograph, SEM, top view showing a micro-channel formed by wet etching thick PECVD SiO 2  through a 1.00 μm wide opening; and 
     FIG. 20 is a Scanning Electron Micrograph, SEM, cross section views and top views showing the closure of the micro-channels with PECVD SiO 2 . 
    
    
     DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS 
     In accordance with the principles of the invention, a biochip chip is fabricated onto an existing CMOS or high-voltage CMOS device. Referring to FIG. 6, as a preparatory step, a conventional CMOS process is used to fabricate a CMOS device  10  up to the dielectric isolation  11  between the last LPCVD polysilicon level  12  and the first metallization level. The isolation dielectric  11 , commonly referred to as the Inter Level Dielectric, ILD, is present before the beginning of the micro-machining steps. A contact is opened through this isolation dielectric to reach the last LPCVD polysilicon layer  12  which is used as an electrode connected to CMOS device for capacitance detection and/or as an electrode connected to high-voltage CMOS devices for fluid movement. 
     After preparing the precursor device, a series of layers are deposited as shown in in the following figures. First, a layer  14  of about 0.10 μm of PECVD Si 3 N 4  is deposited on layer  12  at 400° C. Next, as shown in FIG. 7 a series of layers are deposited on layer  14 . First a layer  16  of about 0.10 μm of CRPVD TiN  16  is deposited at 400° C. After this, a layer  18  of about 10.0 μm of PECVD SiO 2  is deposited at 400° C. 
     Next, a layer  20  about 0.10 μm of CRPVD TiN at 400° C. is deposited on layer  18 . In the next step, a layer  22  of about 0.40 μm of PECVD Si 3 N 4  is deposited on layer  20  at 400° C. Subsequently, a layer  24  of about 0.20 μm of CRPVD TiN at 400° C. 
     In the next step, as shown in FIG. 8, a first micro-machining mask is applied to define a MEMS region, and this is followed by the anisotropic reactive ion etching (Anisotropic RIE) of the CRPVD TiN/PECVD Si 3 N 4 /CRPVD TiN sandwich  20 ,  22 ,  24 , followed by the partial anisotropic RIE of the PECVD SiO 2  layer  18  to form a shoulder  17 . 
     Subsequently, as shown in FIG. 9, a 2 nd  micro-machining mask is applied to define Isotropic Wet Etching openings  26 . This is followed by an anisotropic RIE of the CRPVD TiN/PECVD Si 3 N 4 /CRPVD TiN sandwich  22 ,  24 ,  26  and followed by the completion of the Anisotropic RIE of the PECVD SiO 2  layer  18  outside the MEMS region as to reach the bottom CRPVD TiN layer  16  at  16   a  and remove the shoulder  17 . The degree of penetration h of the anisotropic etch into the PECVD SiO 2  layer  18  of the future micro-channel is not critical. 
     Next, as shown in FIG. 10, a layer  28  of about 0.10 μm of CRPVD TiN is deposited on layer  26  at 400° C. Then, as shown in FIG. 11, an Anisotropic RIE of the CRPVD TiN layer  28  is performed to provide CRPVD TiN ‘spacers’  30  on vertical side-walls while removing the bottom layer to form openings where an Isotropic Wet Etching will be performed and also to remove the portion  28   a  extending over shoulder  16   a.  It will be understood that only one opening is shown in FIG. 11, although typically several will be present. 
     In the next step, shown in FIG. 12., an Isotropic Wet Etch is performed on the PECVD SiO 2    18  using either a mixture of Ethylene Glycol, C 2 H 4 O 2 H 2 , Ammonium Fluoride, NH 4 F, and Acetic Acid, CH 3 COOH, or alternately a mixture of Ammonium Fluoride, NH 4 F, Hydrofluoric Acid, HF, and Water, H 2 O, to define the micro-channels  34 . These two Isotropic Wet Etchings are selective to CRPVD TiN which is used to protect the upper PECVD Si 3 N 4  layer  22 . 
     Following the Isotropic Wet Etching, the CRPVD TiN/PECVD Si 3 N 4 /CRPVD TiN sandwich is suspended over the micro-channels  34 . The mechanical properties and relative thickness of the CRPVD TiN layers  20 ,  22  and PECVD Si 3 N 4  layer  22  are adjusted such that the structure is mechanically stable, i.e. does not bend-up or bend-down over the defined micro-channel, does not peel-off the edges of the underlying PECVD SiO 2 , does not break-down or collapse. FIG. 18 shows a Scanning Electron Micrograph, SEM, cross sectional view demonstrating the excellent mechanical stability of a TiN layer to be suspended over the micro-channel. The pictures are for SEM purposes only and do not describe the optimum device. FIG. 18 shows a Scanning Electron Micrograph, SEM, top view demonstrating a micro-channel formed by wet etching thick PECVD SiO 2  through a 1.00 μm wide opening. The picture is for SEM purpose only and does not describe the optimum device. 
     In the next step shown in FIG. 13, the Isotropic Wet Removal of the CRPVD TiN is performed using a mixture of Ammonium Hydroxide, NH 4 OH, Hydrogen Peroxide, H 2 O 2 , and Water, H 2 O. This Isotropic Wet Removal is selective to the PECVD SiO 2  and to the PECVD Si 3 N 4 . Following the Isotropic Wet Etching, the PECVD Si 3 N 4  layer is suspended over the micro-channels so its mechanical properties and thickness are adjusted such that the layer is mechanically stable, i.e. does not bend-up or bend-down over the defined micro-channel, does not peel-off the edges of the underlying PECVD SiO 2 , does not break-down or collapse. 
     In the following step, shown in FIG. 14, the closure of the opening  26  is effected with the deposition of a layer  40  of about 1.40 μm of PECVD SiO 2  at 400° C. This is possible because the natural overhang of PECVD SiO 2  on vertical surfaces allows a lateral growth of deposited material on these surfaces and ultimately, a closure of the openings. This closure of openings with PECVD SiO 2  is critical because it allows the formation of an enclosed micro-channel  34  without the need for bonding of two substrates, and unlike the prior art permits the fabrication of active micro-channels in contrast to opened micro-reservoirs. Some PECVD SiO 2  material  41  is deposited at the bottom of the micro-channel over the electrode  12 . FIG. 19 shows Scanning Electron Micrograph, SEM, cross section views and top views demonstrating the closure of the micro-channels with PECVD SiO 2 . Again, the pictures are for SEM purpose only and yet do not describe the optimum device. 
     In the next step shown in FIG. 15, a 3 rd  micro-machining mask is applied to define the Isotropic Wet Etching of the upper PECVD SiO 2  where PVD Al-alloy electrodes will later be defined. This Isotropic Wet Etching of the upper PECVD SiO 2  using either a mixture of Ethylene Glycol, C 2 H 4 O 2 H 2 , Ammonium Fluoride, NH 4 F, and Acetic Acid, CH 3 COOH, or alternately a mixture of Ammonium Fluoride, NH 4 F, Hydrofluoric Acid, HF, and Water, H 2 O, is selective to the underlying PECVD Si 3 N 4  layer inside as well as outside the MEMS region an leaves a bridge of SiO 2    40  a closing the opening  26 . 
     Next, as shown in FIG. 16, the deposition of PVD Ti/CRPVD TiN/PVD Al-alloy/CRPVD TiN structure  42  at 400° C. is performed over the MEMS region to form as upper electrodes, as well as over the non-MEMS region, to form interconnections. 
     In the final step shown in FIG. 17, an Anisotropic RIE is performed on the of the PVD Ti/CRPVD TiN/PVD Al-alloy/CRPVD TiN layer  42 , which defines upper electrodes in the MEMS region as well as interconnections over the non-MEMS region. 
     The combination of MEMS regions and non-MEMS regions now defines a biochip which can then be completed by processing the remaining standard CMOS manufacturing steps. 
     The person skilled in the art will understand that many variations to the process described are possible. For example, the substrate could have no active device at all and being used as a passive substrate. In that case, the micro-machining steps to achieve the closed micro-channels would provide a passive device which still has the advantage of providing an enclosed micro-channel without using thermal bonding with a second substrate. Examples of suitable substrates are: Silicon, Quartz, Sapphire, Alumina, acrylonitrile-butadiene-styrene copolymer, polycarbonate, polydimethylsiloxane (PDMS), polyethylene, polymethylmethacrylate (PMMA), polymethylpentene, polypropylene, polystyrene, polysulfone, polytetrafluoroethylene (PTFE), polyurethane, polyvinylchloride (PVC), polyvinylidine fluoride (PVF). 
     The substrate could contain various types of Low-Voltage devices including: sensitive N-type MOS, sensitive P-Type MOS, high speed NPN Bipolar, high speed PNP Bipolar, Bipolar-NMOS, Bipolar-PMOS or any other semiconductor device capable of low signal detection and/or high speed operation. Alternatively, the substrate could contain various types of High-Voltage devices including: N-type Double Diffused Drain MOS, P-type Double Diffused Drain MOS, N-type Extended Drain MOS, P-type Extended Drain MOS, Bipolar NPN, Bipolar PNP, Bipolar-NMOS, Bipolar-PMOS, Bipolar-CMOS-DMOS, Trench MOS or any other semiconductor device capable of high voltage operation at voltages ranging from 10 to 2000 volts. 
     The substrate could be have a compound semiconductor portion capable of on-chip opto-electronic functions such as laser emission and photo-detection. In that case, the substrate could be: Silicon with such on-chip opto-electronic functions, III-V compound semiconductor, II-VI compound semiconductor, II-IV compound semiconductor or combinations of II-III-IV-V semiconductors. 
     The lower polysilicon or Al-alloy capacitor electrode of Step  0  could be replaced by other electrically conductive layers, such as: Copper, Gold, Platinum, Rhodium, Tungsten, Molybdenum, Silicides or Polycides. 
     The Si 3 N 4  layer  14  could be made thicker or thinner if the selectivity of the Wet Etching (FIG. 12) is poorer or better to prevent excessive etch of the electrode located under this Si 3 N 4  layer or it could simply be eliminated if the fluid has to be in physical contact with the electrode located under this Si 3 N 4  layer. 
     The sacrificial TiN layer  16  could be made thicker, thinner or simply eliminated if the selectivity of the Wet Etching (FIG. 17) is poorer, better or simply good enough to prevent excessive etch of the material located under this sacrificial TiN layer, or it simply be eliminated if the fluid to be present inside the micro-channel has to be in physical contact with the electrode located under this TiN layer. The SiO 2  layer  18  of the micro-channel defined could be made thicker or thinner than 10.0 μm depending upon the required size of micro-channel. Alternatively, this SiO 2  material could be replaced by a deposited thin/thick polymer film (using plasma-polymerization or other thin/thick polymer film deposition technique) such as: acrylonitrile-butadiene-styrene copolymer, polycarbonate, polydimethylsiloxane (PDMS), polyethylene, polymethylmethacrylate (PMMA), polymethylpentene, polypropylene, polystyrene, polysulfone, polytetrafluoroethylene (PTFE), polyurethane, polyvinylchloride (PVC), polyvinylidine fluoride (PVF). In this case a suitable Isotropic Wet Etching selective to the other layers has to be developed to define the micro-channel into the thin/thick polymer film; the same thin/thick polymer film deposition technique could be used to ensure the closure of the openings over the micro-channels; lower metallization temperatures would have to be used to prevent the thermal decomposition of the polymeric films. 
     The SiO 2  material of the micro-channel  18  could be replaced by a spun-on polyimide layer. In this case an Isotropic Wet Etching selective to the other layers would have to be used as to allow the formation of the micro-channel into the polyimide film; the same thin/thick polymer film deposition technique could be used to ensure the closure of the openings over the micro-channels; lower metallization temperatures would have to be used to prevent the thermal decomposition of the polyimide film. 
     The SiO 2  material  18  could also be alloyed with different elements such as: Hydrogen, Boron, Carbon, Nitrogen, Fluorine, Aluminum, Phosphorus, Chlorine, or Arsenic. 
     This PECVD SiO 2  material  18  could be deposited by technique other than PECVD, including: Low Pressure Chemical Vapor Deposition, LPCVD, Metal Organic Chemical Vapor Deposition, MOCVD, Electron Cyclotron Resonance Deposition, ECRD, Radio Frequency Sputtering Deposition, RFSD. 
     The sacrificial TiN layer  20  could be made thicker, thinner or simply eliminated if the selectivity of the Wet Etching (FIG. 12) is poorer, better or simply good enough to prevent excessive etch of the material located over this sacrificial TiN layer. 
     The sacrificial TiN layers  20 ,  24  and  28  could be replaced by another sacrificial layer having mechanical properties preventing warpage, delamination, cracking or other degradation of the suspended structured excellent selectivity to Isotropic Wet Etching solutions used to define the micro-channels. 
     The sacrificial CRPVD TiN layers could be deposited by another technique, including: Metal Organic Chemical Vapor Deposition, MOCVD, Low Pressure Chemical Vapor Deposition, LPCVD, Plasma Enhanced Chemical Vapour Deposition, PECVD, Long Through Deposition, LTD, Hollow Cathode Deposition, HCD, and High Pressure Ionization Deposition, HPID. 
     The upper Si 3 N 4  layer  22  could be made thicker or thinner than 0.40 μm depending on its mechanical properties and on the mechanical properties of the surrounding materials to prevent mechanical problems such as plastic deformation, peeling, cracking, de-lamination and other such problems in the etching step shown in FIG.  12 . 
     The sacrificial TiN layer  23  could be made thicker, thinner or simply eliminated if the selectivity of the Wet Etching of FIG. 12 is poorer, better or simply good enough to prevent excessive etch of the material located under this sacrificial TiN layer. 
     The partial Anisotropic RIE shown in FIG. 8 could be eliminated if there is no need to define MEMS regions and non-MEMS regions in the device. 
     The deposition and partial RIE of the CRPVD TiN respectively illustrated in FIG.  10  and FIG. 11 providing CRPVD TiN ‘spacers’ on vertical side-walls of the openings could be eliminated if the selectivity of the Wet Etching shown in 
     FIG. 12 is such that there is no need of having this CRPVD TiN ‘spacers’ on vertical side-walls of the openings. 
     The sacrificial TiN layer  28  shown FIG. 10 could be made thicker or thinner if the selectivity of the Wet Etching shown in FIG. 12) is poorer or better to prevent excessive etch of the material located behind this sacrificial TiN layer. 
     The Wet Isotropic Etching of PECVD SiO 2  shown in FIG. 12 could be performed using other liquid mixtures than either: a) the C 2 H 4 O 2 H 2 , NH 4 F, and CH 3 COOH, or alternately b) NH 4 F, HF, and H 2 O, to properly define the micro-channels. Any other Isotropic Wet Etchings of PECVD SiO 2  could be used if they are selective enough to the bottom layer of  14  (or to the bottom electrode 12  if no such bottom layer is used) and to the combination of layers becoming suspended during this Isotropic Wet Etching. 
     The Isotropic Wet Removal of the CRPVD TiN shown in FIG. 13 can be eliminated if sacrificial CRPVD TiN is not used in the sequence. The Isotropic Wet Removal of the CRPVD TiN shown in FIG. 13 could also be performed using other liquid mixtures than NH 4 OH, H 2 O 2 , and H 2 O if the Isotropic Wet Removal is selective to the PECVD SiO 2  and to the other layers in contact with the Isotropic Wet Removal. 
     The SiO 2  material of the micro-channel shown in FIG. 14 could be made thicker or thinner than 1.40 μm depending upon the size of opening to be filled. 
     The SiO 2  material of the micro-channel shown in FIG. 14 could be replaced by a deposited polymer film (using plasma-polymerization or other thin/thick polymer film deposition technique) such as: acrylonitrile-butadiene-styrene copolymer, polycarbonate, polydimethylsiloxane (PDMS), polyethylene, polymethylmethacrylate (PMMA), polymethylpentene, polypropylene, polystyrene, polysulfone, polytetrafluoroethylene (PTFE), polyurethane, polyvinylchloride (PVC), polyvinylidine fluoride (PVF). The SiO 2  material of the micro-channel could also be alloyed with different elements such as: Hydrogen, Boron, Carbon, Nitrogen, Fluorine, Aluminum, Phosphorus, Chlorine, or Arsenic. 
     The PECVD SiO 2  material of the micro-channel shown in FIG. 14 could be deposited by another technique than PECVD, including: Low Pressure Chemical Vapor Deposition, LPCVD, Metal Organic Chemical Vapor Deposition, MOCVD, Electron Cyclotron Resonance Deposition, ECRD, Radio Frequency Sputtering Deposition, RFSD and could incorporate the use of a filling technique such as Spin-On Glass, SOG, as to provide a smooth seamless upper surface. 
     The Isotropic Wet Etching of the upper PECVD SiO 2  shown in FIG. 15 could be performed using other liquid mixtures than: a) the C 2 H 4 O 2 H 2 , NH 4 F, and CH 3 COOH, or alternately b) NH 4 F, HF, and H 2 O. Other Isotropic Wet Etchings could be used if selective enough to the bottom suspended layer of FIG.  13 . 
     The Isotropic Wet Etching of the upper PECVD SiO 2  shown in FIG. 15 could be replaced by a suitable Dry Etch if such an etch is selective enough to the bottom suspended layer of FIG.  13 . 
     The upper Al-Alloy electrode shown in FIGS. 16 and 17 could be eliminated to minimize the number of micro-machining steps. 
     The upper Al-Alloy electrode shown in FIG. 16 could be replaced by a higher melting point conductive layer if the other layers can be combined in such a way to prevent mechanical problems such as plastic deformation, peeling, cracking, de-lamination and other such high temperature related problems. In that case, the 450° C. temperature limitation of the described micro-machining steps could be increased to 750° C. without degradation of the underlying CMOS and high-voltage CMOS devices. 
     The upper PVD Ti/CRPVD TiN/PVD Al-alloy/CRPVD TiN electrode shown in FIG. 16 could be replaced by LPCVD polysilicon, at temperatures ranging from 530 to 730° C. or by Plasma Enhanced Chemical Vapour Deposited polysilicon, PECVD polysilicon from 330 to 630° C. if the other layers can be combined in such a way as to prevent mechanical problems such as: plastic deformation, peeling, cracking, de-lamination and other high temperature related problems. In that case, the 450° C. limitation of the described micro-machining steps could be increased to 750° C. without degradation of the underlying CMOS and high-voltage CMOS devices. 
     The upper PVD Ti/CRPVD TiN/PVD Al-alloy/CRPVD TiN shown in FIG. 16 could also be replaced by another interconnect structure and deposited at another temperature than at 400° C. 
     The invention may be applied in applications which involve the use of active (i.e. on-chip electronics) micro-channels, such as micro-fluidics applications other than the mentioned detection and/or fluid movement; Micro-chemical detection/analysis/reactor systems; Micro-biological detection/analysis/reactor systems; Micro-bio-chemical detection/analysis/reactor systems; Micro-opto-fluidics systems; Micro-fluid delivery systems; Micro-fluid interconnect systems; Micro-fluid transport systems; Micro-fluid mixing systems; Micro-valves/pumps systems; Micro flow/pressure systems; Micro-fluid control systems; Micro-heating/cooling systems; Micro-fluidic packaging; Micro-inkjet printing; Laboratory-on-a-chip, LOAC, devices; and Other MEMS requiring micro-channels; Other MEMS requiring an enclosed channel. 
     The invention may also be applied to applications which involve the use of passive (i.e. off-chip electronics) micro-channels, such as Micro-chemical detection/analysis systems; Micro-biological detection/analysis systems; Micro-bio-chemical detection/analysis systems; Micro-opto-fluidics systems; Micro-fluid delivery systems; Micro-fluid interconnect systems; Micro-fluid transport systems; Micro-fluid mixing systems; Micro-valves/pumps systems; Micro flow/pressure systems; Micro-fluid control systems; Micro-heating/cooling systems; Micro-fluidic packaging; Micro-inkjet printing; Laboratory-on-a-chip, LOAC, devices; Other MEMS requiring micro-channels; and Other MEMS requiring an enclosed channel. 
     The invention relates to an improved fabrication technique for micro-channel biochip devices, preferably active devices from an active micro-machined silicon substrate that results in a sophisticated biochip device which can perform, via fluid movement into micro-channels, various fluidics, analysis and data communication functions without the need of an external fluid processor in charge of fluid movement, analysis and data generation.