Classifications

• • G—PHYSICS
  • G01—MEASURING; TESTING
  • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
  • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
  • G01T1/29—Measurement performed on radiation beams, e.g. position or section of the beam; Measurement of spatial distribution of radiation
  • G01T1/2914—Measurement of spatial distribution of radiation
  • G01T1/2921—Static instruments for imaging the distribution of radioactivity in one or two dimensions; Radio-isotope cameras
  • G01T1/2928—Static instruments for imaging the distribution of radioactivity in one or two dimensions; Radio-isotope cameras using solid state detectors

Definitions

• the present invention is directly applicable to both healthcare and scientific fields, such as, molecular imaging.
• healthcare previous attempts at replacing conventional x-ray photography with digital imaging systems such as computer tomography (CT) and magnetic resonance imaging (MRI) have been somewhat limited because of the extremely high detection sensitivity required.
• CT computer tomography
• MRI magnetic resonance imaging
• CT and MRI digital imaging techniques it has been estimated that over 90% of the image diagnostic cases in healthcare continue to be provided by conventional x-ray photography.
• An increase in sensitivity also offers many advantages which can be exploited in scientific fields such as x-ray crystallography, electron microscopy and the imaging of labeled molecules.
• complicated molecular structures can be analyzed by x-ray diffraction imaging much faster than conventional scintillation counting.
• the radiation source intensity required is significantly lower which allows transmission electron microscopy without damaging the sample with electron rays. That is, organic crystals and biopolymers are not broken down during analysis with an electron microscope, thereby allowing the use of the full theoretical resolution of electron microscopes.
• molecular imaging it is often desirable to rapidly detect and quantify one or more molecular structures in a sample.
• the molecular structures typically comprise ligands, such as cells, antibodies and anti-antibodies.
• Ligands are molecules which are recognized by a particular receptor. Ligands may include, without limitation, agonists and antagonists for cell membrane receptors, toxins, venoms, oligo-saccharides, proteins, bacteria, and monoclonal antibodies. For example, a DNA or RNA sequence analysis is very useful in genetic and disease diagnosis, toxicology testing, genetic research, agriculture and pharmaceutical development. Likewise, cell and antibody detection is important in disease diagnosis.
• Autoradiography whereby the molecular constituents are labeled with radioisotope tags such as 32 P and 35 S, and subsequently exposed to photographic film.
• Autoradiography provides a moderate resolution image over a relatively large format area, but is plagued by several disadvantages. Due to the relative insensitivity of photographic film to beta particles, the time required for exposure can vary from hours to days. The exposure can be accelerated with the use of intensifying screens, yet spatial resolution is significantly degraded. Typical spatial resolution for autoradiography is on the order of 1 to 10 millimeters. In addition, the resulting photographic image has to be read by a digital scanner for automation purposes.
• Gas phase ionization beta detection is another procedure for imaging radiolabeled molecules as disclosed in the following patent;
• Emitting Radionuclides United States Patent Number: 4,670,656, June 2, 1987, (incorporated by reference herein) .
• beta particles are detected in two separate phases, and the source of beta emission is then calculated by back propagation from the detector plates to the beta source. Since the beta particles are emitted at all angles from the surface horizontal, the back propagation results in a blurring effect that limits the resolution, and is a function of the distance between the detector and the sample.
• the spatial resolution is on the order of 0.1 to 1 millimeters (a factor of 10 better than film) and provides a quantitative digital image.
• the sensitivity is approximately 10 to 100 times better than film, yielding quantitative digital images at least 10 times faster than film (minutes to hours) .
• D. Storage Phosphor Screen Technology Another method of quantitative detection and imaging of radiolabeled molecules is the storage phosphor screen technology, or phosphorimagers.
• a screen of phosphor is placed in a metastable state when exposed to a radioactively labeled sample. Following exposure, the screen is read by exciting the phosphor by a laser and imaging the photons emitted as the electrons return to the ground state.
• Both strong 32 P and weak ( 14 C and 35 S) beta particles can be imaged.
• the spatial resolution and sensitivity is comparable to the gas phase beta detectors, and offers many advantages.
• the variable limiting the number of isotopic scans is the number of imager plates. In essence many samples can be placed on a number of imaging plates.
• CCD charge- coupled-device
• Advantages of a CCD-based detection and quantitative imaging approach include: 1) avoidance of mutagenic radioactive labels, 2) high sensitivity (comparable to PMT) , 3) fast exposure time (seconds) , 4) linear response over wide dynamic range (5 orders of magnitude) , 5) low noise, 6) high quantum efficiency, and 7) fast data acquisition (megapixels/sec) .
• the present invention provides an ultrasensitive detection, quantitative imaging and spectroscopy method and apparatus that yields high resolution digital images of the spatial distribution of particle emissions from relatively large format samples in a minimal amount of time and expense.
• the apparatus is comprised of a lens-less imaging array comprising a plurality of solid state imaging devices, such as an array of CCDs, charge injection devices (CIDs) , photodiode arrays, amorphous silicon sensors or the like.
• the array is disposed in close proximity to the sample and is comparable in size to the area of the sample to be imaged. In this manner a relatively large format digital image of the spatial distribution of sample emission or absorption is produced without requiring the use of one or more lenses between the sample and the imaging array.
• the apparatus offers 1) high sensitivity (10 3 to 10 4 times more than photographic film, 10 - 100 times more than gas phase ionization detection and phosphorimagers) , 2) high throughput (seconds instead of minutes to hours for gas phase ionization detectors and phosphorimagers, and hours to days for photographic film) , 3) linear response over a wide dynamic range (4 to 5 orders of magnitude) , 4) low noise, 5) high quantum efficiency and 6) fast data acquisition. Moreover by placing the imaging array in proximity to the sample, the collection efficiency is improved by a factor of at least 10 over any lens-based technique such as found in conventional CCD cameras.
• the sample is in near contact with the detector (imaging array) , eliminating conventional imaging optics such as lenses and mirrors.
• the inventive apparatus can be used for detecting and quantitatively imaging radioisotope, fluorescent, and chemiluminescent labeled molecules, since a lens-less CCD array apparatus is highly sensitive to both photons and x- ray particles. Hence a single imaging instrument can be used in conjunction with numerous molecular labeling techniques, ranging from radioisotopes to fluorescent dyes.
• the first embodiment entails a static platform whereby a plurality of imaging devices are arranged in a relatively large format area comparable to the sample size.
• the second category of embodiments of the invention entails a dynamic platform that enables a smaller set of imaging devices to image a relatively large format sample by moving either the array of imaging devices or sample, relative to one another.
• the dynamic embodiment of the invention generally concerns a method and apparatus for ultrasensitive detection, high resolution quantitative digital imaging and spectroscopy of the spatial and/or temporal distribution of particle emissions or absorption from/by a sample in a relatively large format.
• the apparatus of the invention includes: a) a large area detector array for producing a relatively large image of detected particle distribution without the use of optical lenses; b) a scanner for moving either the sensor array or the sample in a manner for efficient imaging; and c) a source of energy for exciting the sample or providing absorption by the sample.
• the ratio of detector array size to sample image is 1 for a static format and less than 1 for a dynamic format.
• FIG. 1A is a schematic sectional view of a portion of a static embodiment of the invention.
• FIG. IB is a plan view of a static embodiment, showing 4 columns of CCD chips.
• FIG. 1C is a plan view of a static embodiment with 4 columns and 5 rows of CCD chips.
• FIG. 2A is a schematic diagram illustrating the geometry of a lens coupled detector system of the prior art.
• FIG. 2B is a schematic diagram illustrating the geometry of a lens-less detector system of the present invention.
• FIG. 3 is a schematic diagram of a dynamic embodiment of the invention.
• FIG. 4 is a schematic of an alternate embodiment of the invention.
• FIG. 5 is a sectional view of a conventional wire bond technique applied to the present device.
• FIG. 6 is a sectional view of a modification of FIG. 5 to accommodate wire bonding of the present detector system.
• FIG. 7 is a sectional view of a low profile wire bond of the present invention.
• FIG. 8 is a sectional view of a detector/sample using the bonding system of FIG. 7.
• FIG. 9 is a sectional view of a detector/sample with a low profile bond and isolated imaging on a dynamic platform.
• FIG. 10 is a sectional view of a detector/sample for a backside illuminated approach.
• a preferred embodiment of a sensor system 10 of the invention consists of a plurality of CCD arrays CCD1...CCDN assembled in a large format module as illustrated in FIGS. 1A-1C.
• Individual CCD arrays are closely aligned and interconnected in particular geometries to form a relatively large (greater than 1cm 2 ) format imaging sensors of the linear array type 10B or the two dimensional row and column type IOC shown in FIGS. IB and 1C respectively.
• Each CCD array CCD1...CCDN is formed, in the conventional manner, by growing and patterning various oxide layers 14 on a Si wafer/substrate 12.
• CCD gate electrodes 10 are then formed by deposition of polysilicon or other transparent gate material on the gate insulator or field oxide 14.
• a dielectric or polymer layer 18, preferably of light transmissive material such as silicon nitride or glass, Si0 2 or polyamide is then formed over the electrodes 16.
• the filter is adapted to block the excitation radiation and pass the secondary emission from the sample 20.
• the sensor module remains fixed with respect to the sample.
• a plurality of imaging devices CCD1...CCDN must be arranged in a module as illustrated in FIGS. IB and 1C.
• the module can be packaged for easy installation to facilitate multiple modules, each for specific applications.
• a sample 20 is placed in proximity to the CCD array sensor 10.
• the sample may be the chest of a patient for clinical radiology applications, or a gel having labeled molecular constituents for analysis.
• the sample can be excited by an external energy source or can be internally labeled with radioisotopes emitting energetic particles or radiation, or photons may be emitted by the sample when labeled with fluorescent and chemiluminescent substances. Conversely, direct absorption may be used to determine their presence. In this case, the absence of illuminating radiation on the detector may constitute the presence of a particular molecule structure.
• the sample can be physically separated from the CCD detector by (an optional) thin isolation plate 22, such as glass or quartz, which is transparent to the particle emission.
• the CCD detection and imaging arrays CCD1-CCDN generate electron-hole pairs in the silicon 12 when the charged particles or radiation of energy ht shown by the "asterisk" 32 arising from or transmitted by the sample are incident (arrows 30) on the CCD gates 16.
• the CCDs can be constructed in a back illuminator format whereby the charged particles are incident in the bulk silicon 12 for increased sensitivity.
• the liberated photoelectrons 34 are then collected beneath adjacent CCD gates 16 and sequentially read out on a display (not shown) by display module 36 in the well-known manner.
• Silicon based CCD's are preferred as the solid state detection and imaging sensor primarily due to the high sensitivity of the devices over a wide wavelength range of from 1 to 10,OO ⁇ A wavelengths. That is, silicon is very responsive to electromagnetic radiation from the visible spectrum to soft x-rays. Specifically for silicon, only 1.1 eV of energy is required to generate an electron-hole pair in the 3000 to HOOoA wavelength range. Thus for visible light, a single photon incident on the CCD gate 16 will result in a single electron charge packet beneath the gate, whereas for soft x-rays, a single beta particle (typically KeV to MeV range) will generate thousands to tens of thousands of electrons.
• a single beta particle typically KeV to MeV range
• the silicon CCD device provides ultrasensitive detection and imaging for low energy alpha or beta emitting isotopes ( 3 H, 14 C, 35 S) as well as high energy alpha or beta emitting isotopes ( 32 P, 125 I) . Consequently, the CCD is both a visible imager (applicable to fluorescent and chemiluminescent labeled molecular samples) and a particle spectrometer (applicable to radioisotope labeled samples as well as external x-ray radiated samples) . In fact the CCD is the only sensor that can provide simultaneous imaging and spectroscopy in the same image.
• the CCDs offer a wide dynamic range (5 orders of magnitude) since the charge packet collected beneath each pixel or gate 16 can range from a few to a million electrons. Furthermore, the detection response is linear over the wide dynamic range which facilitates the spectroscopy function, since the amount of charge collected is directly proportional to the incident photon energy. Hence, no reciprocity breakdown occurs in CCDs, a well-known limitation in photographic film.
• the first approach requires either external x-ray sample excitation or the attachment of a radioactive label to the sample constituents.
• the pixels (gates) 16 on the CCD arrays accumulate electrical charge proportional to the radiation products absorbed from the sample. Hence, charge particles are detected almost instantaneously by automatically addressing and reading the charge.
• the SNR for the lens-less CCD approach used with x- ray excitation can be expressed once the integration time is determined. Assume the sample is labeled with 32 P.
• N e ( t) - N t A J (l-e - t/r )
• the dark current contribution to the noise can be decreased and crosstalk suppressed by framing the CCD very quickly using a shorter integration time ⁇ «t .
• the CCD pixels become single event detectors since the number of collected photoelectrons in a pixel remains larger than either the dark current or read noise and the probability of one or more events is small in the duration of T seconds.
• the read noise increases, the charge-to-voltage noise associated with a single pixel readout can be less than 10 electrons.
• the pixels can be designed to minimize the variation in electrons collected per beta particle event.
• Such technique is well suited to the x-ray excitation mode since the beta particle events are relatively infrequent and easily distinguished from noise frames. Moreover, crosstalk is further suppressed by the technique since the probability of beta events occurring simultaneously in neighboring sample component sites decreases with decreasing integrating time. The use of lower energy beta particles ( 35 S) will also suppress crosstalk. Therefore the density of the labeling can be increased to accommodate thousands of distinct molecular components on a single sample when employing single event detection.
• a 32 P labeled sample can be detected in seconds time throughout thousands of sites on a large format CCD imaging module operating at room temperature with sufficient SNR.
• a similar analysis can be conducted for a sample externally excited by a x-ray source by substituting the radiated energy level incident on the imaging module for the signal electron density S. ' Fluorescent Excitation
• the second approach analyzed involves the use of fluorescent-labeled receptors attached to the sample components.
• the fluorescent labels can be attached covalently or through intercalation.
• the detection procedure for using the fluorescent labels begins by analyzing the optical absorption spectrum of the chosen label.
• the regions in the spectra of high absorption are used to select the illumination source wavelength.
• an ultraviolet (UV) light source provides maximum absorption and emission is in the red spectrum (e.g., 630 nm) .
• UV ultraviolet
• These spectral regions of excitation and detection enhance SNR, since the polysilicon gates of the CCD substrate naturally absorb UV light and the line grating fabricated on the chip can provide optical filtering near the 630 nm region. Consequently, sensitivity can be improved by employing fluorescent markers, choosing the optimal excitation wavelength and the corresponding detection filter implemented directly on the CCD chip.
• the charge accumulated at the pixels is proportional to the number of photons detected from the fluorescence of the molecular constituents of the sample.
• the power density required of the illumination source for a one second integration time is given by:
• the excitation required to ensure sensitive detection can be met in theory using a 61 ⁇ W/cm 2 UV source.
• This can be provided by a filtered mercury arc, or else by one of several relatively inexpensive UV laser sources.
• Chemi luminescent Excitation is the conversion of chemical energy into electromagnetic radiation. In these types of reactions, electrons are excited via a chemical reaction, and light is emitted upon return of the excited electrons to the ground state. Unlike other chemiluminescent modalities, enzyme-catalyzed 1,2-dioxetane derivatives can produce a light signal that can last from hours to days. The wavelength of emitted light is near 477 nm, and the emission can be controlled by controlling the pH.
• the SNR for the lens-less CCD approach for a 0.1 second integration time in the chemiluminescent mode of operation follows the expression obtained for the fluorescent approach and is given by (assuming negligible read noise)
• the values for the enzymatic reaction turnover rate and chemiluminescent quantum yield are typical for the dioxetane reagent.
• the chemiluminescent approach appears feasible for detecting thousands of molecular constituents within a sample in proximity to the CCD imaging module operating at room temperature.
• the collection efficiency ⁇ is measure of an instrument's capability to capture electromagnetic radiation and is primarily a function of geometry.
• the geometrical configurations for lens-based instruments (epifluorescent microscope, confocal microscope, CCD camera and the like) and the lens-less CCD imaging module are illustrated in FIGS. 2A and 2B, respectively. Collection efficiency is typically expressed as a ratio of solid angles
• FIG. 3 One of two preferred embodiments for housing the above described detection and imaging sensor is illustrated schematically in FIG. 3.
• the embodiment of FIG. 3 consists of: a) a relatively large format imaging sensor 100 formed of a CCD module 110 comprised of a plurality of smaller imaging devices CCD1...CCDN, each device having a plurality of photosensitive pixels 102; b) scanner apparatus 104 for relative movement of the module 110 with respect to a molecular sample 106 in a manner for efficient imaging; c) light source 108 for exciting the molecular sample; d) an array driver circuit 120 for driving the sensor array 110 which includes clocking, biasing, and electronic gating of the pixel electrodes in CCD1...CCDN; e) a receiving circuit 122 for obtaining the digital image from the sensor array 110 which includes preamplification, amplification, analog to digital conversion, filtering, multiplexing, sampling and holding functions; f) a data processor 124 for processing the imaging data including contrast enhancement and parameter estimation; and g) display means 126 for
• excitation sources 108 may be employed in the instrument.
• An external x-ray source used for conventional radiography can be employed for medical x-ray imaging.
• UV excitation may be provided by a lamp or laser, mounted above or below the sample.
• no excitation source is required for radioisotope and chemiluminescent labeled samples.
• the dynamic platform embodiment of FIG. 3 enables the imaging module or sample to be moved using a scanning mechanism such as a step motor mechanically coupled to platform 130.
• a scanning mechanism such as a step motor mechanically coupled to platform 130.
• a plurality of imaging devices 110 can be arranged in a module of columns to minimize discontinuity.
• the scanning can be accomplished with intentional overlapping to provide continuous high resolution imaging across the entire large format sample area.
• FIG. 4 An additional excitation method is illustrated in FIG. 4 where a laser 200 is projected through a cylindrical lens system 202 to form a beam 204 of excitation on the sample 206 at the Brewster angle to minimize reflective losses. Reflection 208 from the concentrated line excitation is then imaged by the nearby sensor module 210 as illustrated.
• imaging array Because physical contact may take place between the imaging array and the substrate sample to be analyzed, means must be used to protect the bond wires which make contact to the imaging device to connect the pixel electrodes to the driver circuits and image receiver circuits, e . g. 120, 122 FIG. 3. These are removed from the immediate location of the imaging array if a device with a frame store array is used; such as described in the Burke et al . , 1991 reference. Imaging of substrates of the same size as, or smaller than, the imaging array can be accomplished with standard wire bonding and some means to prevent the substrate from touching the device in the neighborhood of the wire bonds. However, if the size restriction of the substrate is removed and substrates which are larger than the size of the 2xN imaging array are allowed, then special means of attaching and protecting the wire bonds must be used.
• FIG. 5 shows a conventional wire bond 600 which loops above the surface of the device to bond to a contact so that contact of the wire bond with the edge 604 of the device 602, and subsequent possible shorting, may be avoided.
• FIG. 6 shows how the large sample substrate 700 must be flexed in order to contact the imaging array so that good resolution is assured, but also clear the epoxy encapsulated bond wire 600' which projects typically 15 mils above the device surface.
• FIG. 7 shows a new method of making bonds in which the bond wires 600'' are brought out approximately parallel to the surface of the device 602'.
• a bead 701 of epoxy is first run along the edge of the device and is allowed to harden before attaching the wires. Also, the land 702 on the circuit board to which the device is bonded is positioned a distance D (the proper distance) from the edge of the device so that the wire 600'' lies nearly flat on the device surface, protruding less than 5 mils above it, and also has a loop sufficient to relieve stresses.
• FIG. 8 shows the epoxy encapsulated wire 600'" with a substrate to be imaged 700 which is flexed to a much lesser extent than in FIG. 6. Alternatively, as in FIG.
• FIG. 9 shows a method which utilizes a transparent isolation plate 22 in conjunction with the low profile bonding technique previously illustrated in FIG. 7.
• the distance D is kept minimal to enable lens-less imaging with minimal distortion.
• a backside illuminated sensor approach shown in FIG. 10 can be applied which enables the electrical connections 900 from the device package 702 to the sensor device 701 to be placed on the opposite side of the device, well away from the sample 800'.
• a minimal distance D b can be achieved between the sample and imaging sensor device 701 to warrant lens-less imaging as described.
• the backside illumination sensor approach also provides more sensitivity since the quantum efficiency is substantially improved by avoiding photo-electron transmission through the polysilicon gates of the sensor array in the device 701.

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• 1995
  • 1995-02-09 JP JP7522366A patent/JPH09509494A/ja active Pending
  • 1995-02-09 EP EP95911678A patent/EP0746778A1/de not_active Ceased
  • 1995-02-09 CA CA 2183978 patent/CA2183978A1/en not_active Abandoned
  • 1995-02-09 WO PCT/US1995/001725 patent/WO1995023348A1/en not_active Application Discontinuation

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