Source: http://www.google.com/patents/US7970458?dq=6760745
Timestamp: 2014-03-15 04:51:14
Document Index: 646406913

Matched Legal Cases: ['Application No. 05813935', 'Application No. 04754292', 'Application No. 200580043930', 'Application No. 2006', 'Application No. 200480021343', 'Application No. 2']

Patent US7970458 - Integrated disease diagnosis and treatment system - Google PatentsSearch Images Maps Play YouTube News Gmail Drive More »Sign inAdvanced Patent SearchPatentsDesigns, implementations, and techniques for optically measuring a sample and integrated systems that provide CT-scan, optical probing and therapy by electromagnetic radiation treatment (e.g. laser, RF, or microwave). Light at different wavelength bands may be used to detect different absorption features...http://www.google.com/patents/US7970458?utm_source=gb-gplus-sharePatent US7970458 - Integrated disease diagnosis and treatment systemAdvanced Patent SearchPublication numberUS7970458 B2Publication typeGrantApplication numberUS 11/253,242Publication dateJun 28, 2011Filing dateOct 17, 2005Priority dateOct 12, 2004Also published asCN101389264A, CN101389264B, EP1804661A2, EP1804661A4, US20060079762, WO2006045013A2, WO2006045013A3Publication number11253242, 253242, US 7970458 B2, US 7970458B2, US-B2-7970458, US7970458 B2, US7970458B2InventorsPeter E. Norris, Feiling Wang, Xiao-Li LiOriginal AssigneeTomophase CorporationExport CitationBiBTeX, EndNote, RefManPatent Citations (90), Non-Patent Citations (25), Referenced by (4), Classifications (24), Legal Events (2) External Links: USPTO, USPTO Assignment, EspacenetIntegrated disease diagnosis and treatment systemUS 7970458 B2Abstract Designs, implementations, and techniques for optically measuring a sample and integrated systems that provide CT-scan, optical probing and therapy by electromagnetic radiation treatment (e.g. laser, RF, or microwave). Light at different wavelength bands may be used to detect different absorption features in the sample. Multiple light sources may be used including tunable lasers.
a bronchoscope comprising a working channel configured for insertion into a passage of a body to reach a target area inside the body;
an optical fiber probe module comprising (1) a probe optic fiber having a portion inserted into the working channel of the bronchoscope and (2) an optical probe head coupled to an end of the probe optic fiber and located inside the working channel, the optical fiber probe module operable to direct probe light to and collect reflected light from the target area in the body through the probe optic fiber and the optical probe head and to obtain information of the target area from the collected reflected light; and
a laser therapy module comprising a power delivery optic fiber having a portion inserted into the working channel of the bronchoscope to deliver a treatment laser beam to the target area,
wherein the probe optic fiber is structured to support light in a first propagation mode and a second, different propagation mode, and the optical fiber probe module further comprises:
a light source to produce the probe light, wherein the probe optic fiber receives and guides the probe light in the first propagation mode,
wherein the optical probe head is coupled to the probe optic fiber to receive the light from the probe optic fiber and to reflect a first portion of the light back to the probe optic fiber in the first propagation mode and direct a second portion of the light to the targeted area, the probe head collecting reflection of the second portion from the target area and exporting to the probe optic fiber the reflection as a reflected second portion in the second propagation mode;
an optical differential delay unit to produce and control a relative delay between the reflected first portion and the reflected second portion received from the probe optic fiber in response to a control signal;
a detection module to receive the reflected first portion and the reflected second portion from the probe optic fiber and to extract information of the target area carried by the reflected second portion; and
a control unit, which produces the control signal to the optical differential delay unit, to set the relative delay at two different bias values to select a layer of material inside the target area to measure an optical absorption of the selected layer.
a computed tomography (CT) module to scan at least a part of the body to obtain CT scan data of the scanned part of the body which is analyzed to identify and locate the target area suspicious of being malignant for further probing and analysis by the optical fiber probe module.
3. The device as in claim 1, wherein the detection module comprises:
4. The device as in claim 3, wherein the first and second optical elements are optical gratings.
5. The device as in claim 1, wherein the detection module comprises a digital signal processor to process information of the target area in the reflected second portion and to generate spectral absorbance data of the target area.
6. The device as in claim 1, wherein the optical differential delay unit comprises:
7. The device as in claim 1, wherein the first and second propagation modes are two orthogonal polarization modes supported by the probe optic fiber, and wherein the detection module comprises:
8. The device as in claim 1, wherein the optical probe head comprises a partial mode converter which sets the reflection from the target in the second propagation mode.
9. The device as in claim 1, wherein the optical probe head comprises:
a partial reflector to reflect the reflected first portion of the probe light and to transmit the second portion of the probe light to the sample; and
a polarization rotator located between the partial reflector and the target area to change a polarization of the reflected second portion in controlling the reflected second portion to be in the second propagation mode.
10. The device as in claim 1, wherein the optical probe head comprises:
a partial reflector to reflect the reflected first portion of the probe light and to transmit the second portion of the probe light to the target area; and
a Faraday rotator located between the partial reflector and the target area to change a polarization of the reflected second portion in controlling the reflected second portion to be in the second propagation mode.
11. The device as in claim 1, wherein the optical probe head comprises:
a quarter wave plate located between the partial reflector and the target to change a polarization of the reflected second portion in controlling the reflected second portion to be in the second propagation mode.
12. The device as in claim 1, wherein the optical fiber probe module further comprises:
an input waveguide to receive the probe light from the light source and to guide the input beam in the first propagation mode;
an output waveguide to receive the reflected first and second portions from the probe optic fiber and to direct the reflected first and second portions to the optical differential delay unit; and
an optical router coupled to the input waveguide, the probe optic fiber, and the output waveguide, the optical router to direct light coming from the input waveguide to the probe optic fiber and light coming from the probe optic fiber to the output waveguide.
13. The device as in claim 12, wherein the optical router comprises:
an optical circulator;
a first beam splitter in the probe optic fiber to transmit light in the first propagation mode and to reflect light in the second propagation mode;
a second beam splitter in the output waveguide to transmit light in the first propagation mode and to reflect light in the second propagation mode; and
a bypass waveguide coupled between the first and the second beam splitters to direct the reflected second portion reflected by the first beam splitter to the second beam splitter which directs the reflected second portion into the output waveguide by reflection.
14. The device as in claim 12, further comprising a tunable optical filter located in one of the input waveguide, the probe optic fiber, and the output waveguide to select a portion of the spectral response of the target area to measure.
15. The device as in claim 1, further comprising a tunable optical filter to filter the probe light to select a portion of the spectral response of the target area to measure.
16. The device as in claim 1, further comprising a tunable optical filter to filter the reflected first and second portions to select a portion of the spectral response of the target area to measure.
wherein the optical fiber probe module further comprises:
a plurality of light sources emitting light at different wavelength bands centered at different wavelengths as the probe light into the probe optic fiber, wherein the optical probe head reflects a first portion of the probe light back to the probe optic fiber in a first propagation mode and directs a second portion of the probe light to the target area, and wherein the probe head collects reflection of the second portion from the target area and exports to the probe optic fiber the reflection as a reflected second portion in a second propagation mode different from the first propagation mode;
18. The device as in claim 17, further comprising:
This application claims the benefit of the U.S. Provisional Patent Application Ser. No. 60/620,793 entitled �Early-Stage Lung Cancer Diagnosis and Treatment System� and filed on Oct. 20, 2004.
This application is a continuation-in-part application of and claims the benefit of U.S. application Ser. No. 10/963,948 entitled �Coherence-Gated Optical Glucose Monitor� and filed on Oct. 12, 2004 now U.S. Pat. No. 7,263,394 which was published as U.S. patent publication No. US-2005-0075547-A1 on Apr. 7, 2005.
This application is also a continuation-in-part application of and claims the benefit of pending U.S. application Ser. No. 11/244,418 entitled �Cross-Sectional Mapping of Spectral Absorbance Features� and filed on Oct. 4, 2005.
The entire disclosures of the above-referenced patent applications are incorporated herein by reference as part of the specification of this application.
BACKGROUND This application relates to devices and techniques for non-invasive optical probing of various substances, and devices, systems and methods for detecting, diagnosing and treating lung disease using the non-invasive optical probing.
Low-coherence light in free-space Michelson interferometers was utilized for measurement purposes. Optical interferometers based on fiber-optic components were used in various instruments that use low-coherence light as means of characterizing substances. Various embodiments of the fiber-optic OCDR exist such as devices disclosed by Sorin et al in U.S. Pat. No. 5,202,745, by Marcus et al in U.S. Pat. No. 5,659,392, by Mandella et al in U.S. Pat. No. 6,252,666, and by Tearney et al in U.S. Pat. No. 6,421,164. The application of OCDR in medical diagnoses in certain optical configurations has come to be known as �optical coherence tomography� (OCT).
SUMMARY This application describes devices, systems and techniques that use non-invasive optical probing and integrated medical diagnosis and treatment systems and techniques based on the non-invasive optical probing. In one implementation, for example, an integrated diagnostic and treatment system is described to include a CT scan unit to locate ailing areas in a body part, a referenced cross-sectional imaging unit to analyze each ailing area, and a laser, RF or microwave irradiation therapy unit to treat a selected ailing area. In another implementation, this application describes an integrated diagnostic/therapeutic system for lung cancer treatment which includes a CT scan unit to locate pulmonary nodule locations; a referenced cross-sectional imaging unit to analyze each pulmonary nodule location; and a laser irradiation therapy unit to optically treat a selected pulmonary nodule location. In yet another implementation, an integrated diagnostic and treatment system is described to include a CT scan unit to locate pulmonary nodule locations; a referenced cross-sectional imaging unit to analyze each pulmonary nodule location; and a microwave ablation therapy unit to treat a selected pulmonary nodule location.
Specific implementations of the above systems and devices are also described. In one example, a medical device includes a bronchoscope comprising a working channel configured for insertion into a passage of a body to reach a target area inside the body; an optical fiber probe module comprising (1) a probe optic fiber having a portion inserted into the working channel of the bronchoscope and (2) an optical probe head coupled to an end of the probe optic fiber and located inside the working channel, the optical fiber probe device operable to direct probe light to and collect reflected light from the target area in the body through the probe optic fiber and the optical probe head and to further obtain information of the target area from the collected reflected light; and a laser therapy module comprising a power delivery optic fiber having a portion inserted into the working channel of the bronchoscope to deliver a treatment laser beam to the target area.
A method for diagnosing and treating a malignant condition of a patient is also described to include performing a computed tomography (CT) scan in a selected body part of the patient to identify locations in the selected body part that are potentially malignant; using an optical probe beam to optically probe the identified locations to further identify malignant locations from benign locations; and delivering radiation energy to each identified malignant location to treat a malignant condition.
This application also describes methods and apparatus for the acquisition of optical spectral absorbance features and their distribution in the cross sections of tissues and other samples using multiple light sources emitting light centered at different wavelengths. In one example, a method for optically measuring a sample is described, where different light sources emitting light at different wavelengths are used to measure the sample. The light at each and every wavelength from the different light sources is directed through a single, common waveguide in a first propagation mode to one sampling location of a sample. The first portion of the guided light in the first propagation mode at a location near the sample is directed away from the sample before the first portion reaches the sample while allowing a second portion in the first propagation mode to reach the sample. A reflection of the second portion from the sample is directed to be in a second propagation mode different from the first propagation mode to produce a reflected second portion. Both the reflected first portion in the first propagation mode and the reflected second portion in the second propagation mode are then directed through the single waveguide. A relative delay between the reflected first portion and the reflected second portion received from the single waveguide is produced. The relative delay between the reflected first portion and the reflected second portion received from the single waveguide are adjusted at two different bias values to select a layer of material inside the sample to measure an optical absorption of the selected layer at each and every wavelength from the different light sources. The light at each and every wavelength from the different light sources is directed through the single waveguide to other sampling locations of the sample to measure the optical absorption of the selected layer at each and every wavelength from the different light sources at each of the sampling locations.
In another example, a device is described to include radiation sources to produce radiation beams at different wavelengths, respectively. A multiplexer is used to receive the radiation beams from the radiation sources and to combine the radiation beams to propagate along a common path. A delivery module is used to direct a part of the combined radiation to a sample and to collect reflected radiation from the sample while reflecting the radiation that does not reach the sample in its vicinity. This device also includes a controllable differential delay device to receive both the reflected radiation from the sample and reflected radiation that does not reach the sample. A demultiplexer is included in this device to receive radiation from the differential delay device and to separate received radiation into a plurality of beams at different wavelengths. The device further includes radiation detectors positioned to respectively receive the beams from the demultiplexer.
In another example, a device described in this application includes means for combining and guiding optical radiation from a plurality of light sources, each emitting at wavelengths within a spectral band different from others, towards a sample through a common optical waveguide; means for reflecting a first portion of the combined radiation away from the sample at its vicinity while directing a second portion of the combined radiation to reach the sample; means for collecting and guiding at least part of the reflected first portion and at least part of a reflected second portion from the sample towards a detection module through the common optical waveguide; means for separating the light into a plurality of spectral bands corresponding to emitting spectral bands of the light sources; and means for directing light radiation of the separated spectral bands to a plurality of light detectors, respectively.
This application also describes an example of a device for optically measuring a sample to include light sources emitting light at different wavelength bands centered at different wavelengths, a single waveguide to receive and guide the light at the different wavelength bands in a first propagation mode, and a probe head coupled to the waveguide to receive the light from the waveguide and to reflect a first portion of the light back to the waveguide in the first propagation mode and direct a second portion of the light to a sample. The probe head collects reflection of the second portion from the sample and exports to the waveguide the reflection as a reflected second portion in a second propagation mode different from the first propagation mode. This device also includes an optical differential delay unit to produce and control a relative delay between the first propagation mode and the second propagation mode in response to a control signal, and a detection module to receive the reflected light radiation in the first and second propagation modes to extract information of the sample carried by the reflected light in the second propagation mode and a control unit. The control unit produces the control signal to the optical differential delay unit and sets the relative delay at two different bias values to select a layer of material inside the sample to measure an optical absorption of the selected layer at each and every wavelength from the different light sources. In one implementation, the detection module may be configured to include an optical device to convert a part of received light in the first propagation mode and a part of received light in the second propagation mode into light in a third propagation mode that propagates along a first optical path. This optical device also converts remaining portions of the received light in the first and the second propagation modes into light in a fourth propagation mode that propagates along a second, different optical path. The detection module also includes a first optical element in the first optical path to separate light at different wavelength bands into a first set of different beams, first light detectors to respectively receive and detector the first set of different beams from the first optical element, a second optical element in the second optical path to separate light at different wavelength bands into a second set of different beams, and second light detectors to respectively receive and detector the second set of different beams from the second optical element.
In yet another example, a device for optically measuring a sample is described to include tunable laser sources emitting light at different wavelength bands centered at different wavelengths. A single waveguide is included to receive and guide the light at the different wavelength bands in a first propagation mode. A probe head is coupled to the waveguide to receive the light from the waveguide and to reflect a first portion of the light back to the waveguide in the first propagation mode and direct a second portion of the light to a sample. The probe head collects reflection of the second portion from the sample and exports to the waveguide the reflection as a reflected second portion in a second propagation mode different from the first propagation mode. A detection module is included to receive the reflected light in the first and the second propagation modes in the waveguide and to extract information of the sample carried by the reflected light in the second propagation mode. A control unit is also included to tune each tunable laser through a corresponding wavelength band to obtain absorption measurements of the sample at different wavelengths within each corresponding wavelength band.
The designs, techniques and exemplary implementations for non-invasive optical probing described in this application use the superposition and interaction of different optical modes propagating along substantially the same optical path inside one or more common optical waveguides. When one of the optical modes interacts with the substance under study, its superposition with the other mode can be used for the purpose of acquiring information about the optical properties of the substance.
In various examples described in this application, optical radiation is not physically separated to travel different optical paths. Instead, all propagation waves and modes are guided along essentially the same optical path through one or more common optical waveguides. Such designs with the common optical path may be advantageously used to stabilize the relative phase among different radiation waves and modes in the presence of environmental fluctuations in the system such as variations in temperatures, physical movements of the system especially of the waveguides, and vibrations and acoustic impacts to the waveguides and system. In this and other aspects, the present systems are designed to do away with the two-beam-path configurations in various interferometer-based systems in which sample light and reference light travel in different optical paths. Implementations of the present systems may be configured to significantly reduce the fluctuations and drifts in the differential phase delay and to benefit some phase-sensitive measurements, such as the determination of the absolute reflection phase and birefringence. In addition, the techniques and devices described in this application simplify the structures and the optical configurations of devices for optical probing by using the common optical path to guide light.
A further example of a device for optically measuring a sample includes an input waveguide, an output waveguide and a probe head. The input waveguide supports a first and a second different propagation modes and is used to receive and guide an input beam in the first propagation mode. The output waveguide supports a first and a second different propagation modes. The probe head is coupled to the input waveguide to receive the input beam and to the output waveguide to export light. The probe head is operable to direct a first portion of the input beam in the first propagation mode into the output waveguide and direct a second portion of the input beam to a sample. In addition, the probe head collects reflection of the second portion from the sample and exports to the output waveguide the reflection as a reflected second portion in the second propagation mode. Furthermore, this device includes a detection module to receive the reflected first portion and the reflected second portion in the output waveguide and to extract information of the sample carried by the reflected second portion.
DETAILED DESCRIPTION Lung cancer is one of the most deadly cancers in the United States. Patients with lung cancer have a relatively low 5-year survival rate of only 10-15% after diagnosis. The lung cancer in many patients is already in the second or third stage and has metastasized to other sites or organs by the time they begin to exhibit symptoms and seek medical treatment. Few are diagnosed in early stages where the survival rate can be much higher, approaching 85% for the stage 1 lung cancer. The conventional annual chest X-ray examination has not shown sufficient sensitivity to reveal the isolated, small (e.g., less than 1 centimeter in diameter) tumors typically found in the stage 1 lung cancer.
{ E A = 1 2 ⁢ ( ⅇ jΓ ⁢ E 001 + rE 002 ) ; E B = 1 2 ⁢ ( ⅇ jΓ ⁢ E 001 + rE 002 ) . ( 1 ) It is assumed that all components in the system, except for the sample 205, are lossless. The resultant intensities of the two superposed modes are
{ I A = 1 2 ⁡ [ E 001 2 + E 002 2 +  r  ⁢ E 001 ⁢ E 002 ⁢ cos ⁡ ( Γ - φ ) ] ; I B = 1 2 ⁡ [ E 001 2 + E 002 2 -  r  ⁢ E 001 ⁢ E 002 ⁢ cos ⁡ ( Γ - φ ) ] , ( 2 ) where φ is the phase delay associated with the reflection from the sample. A convenient way to characterize the reflection coefficient r is to measure the difference of the above two intensities, i.e.
A Ω =E 001 E 002 J 1(M)|r| sin φ; (5a) A 2Ω =E 001 E 002 J 2(M)|r| cos φ, (5b)
{ E s = 1 2 ⁢ E , E p = 1 2 ⁢ E . ( 6 ) where the electric field transmitting the polarizer is denoted as E. It should be appreciated that the light has a finite spectral width (broadband or partially coherent). The fields can be described by the following Fourier integral:
{ E s = 1 2 ⁢ E , E p = 1 2 ⁢ rEⅇ jΓ . ( 8 ) The light that passes through Polarizer 540 can be expressed by
E a = 1 2 ⁢ ( E s + E p ) = 1 2 ⁢ E ⁡ ( 1 + rⅇ j ⁢ ⁢ Γ ) . ( 9 ) The intensity of the light that impinges on the photodetector 550 is given by:
I = E a ⁢ E a * = 1 4 ⁢  E  2 ⁡ [ 1 +  r  2 + 2 ⁢  r  ⁢ cos ⁡ ( Γ + δ ) ] . ( 10 ) where phase angle δ reflects the complex nature of the reflection coefficient of the sample 205 and is defined by
I = 1 +  r  2 4 ⁢  E  2 +  r  2 ⁢  E  2 ⁢ cos ⁡ [ M ⁢ ⁢ sin ⁡ ( Ω ⁢ ⁢ t ) + φ + δ ] . ( 12 ) where phase angle φ is the accumulated phase slip between the two modes, not including the periodic modulation due to the modulator 520. The VDGD 530 or a static phase shift in the modulator 520, may be used to adjust the phase difference between the two modes to eliminate φ.
A Ω=0.5|E| 2 J 1(M)|r| sin δ; (13a) A 2Ω=0.5|E| 2 J 2(M)|r| cos δ, (13b)
I = ∫ { 1 +  r  2 4 ⁢  E ⁡ ( λ )  2 +  r  2 ⁢  E ⁡ ( λ )  2 ⁢ cos ⁡ [ M ⁢ ⁢ sin ⁡ ( Ω ⁢ ⁢ t ) + φ ⁡ ( λ ) + δ ] ⁢ ⅆ λ . ( 14 ) It is easy to see that if the range of φ(λ) is comparable to π for the bandwidth of the light source no oscillation in I can be observed as oscillations for different wavelengths cancel out because of their phase difference. This phenomenon is in close analogy to the interference of white light wherein color fringes are visible only when the path difference is small (the film is thin). The above analysis demonstrates that the use of a broadband light source enables range detection using the proposed apparatus. In order to do so, let the s-wave to have a longer optical path in the system compared to the p-wave (not including its round-trip between Probing Head and Sample). For any given path length difference in the system there is a matching distance between Probing Head and Sample, z, that cancels out the path length difference. If an oscillation in I is observed the p-wave must be reflected from this specific distance z. By varying the path length difference in the system and record the oscillation waveforms we can therefore acquire the reflection coefficient r as a function of the longitudinal distance z, or depth. By moving Probing Head laterally, we can also record the variation of r in the lateral directions.
A II(λ)=r II e −μ g (λ)z I −2μ h (λ)z II , (16)
A II ⁡ ( λ ) A I ⁡ ( λ ) = r II r I ⁢ ⅇ - 2 ⁢ μ h ⁡ ( λ ) ⁢ z II . ( 17 ) Notably, this equation provides the information on the absorption characteristics of the layer of interest only and this allows measurement on the layer. This method thus provides a �coherence gating� mechanism to optically acquire the absorbance spectrum of a particular and designated layer beneath a sample surface.
The above �coherence gating� may be used to overcome the difficulty in other methods for monitoring glucose. For glucose monitoring, the designated layer may be the dermis layer where glucose is concentrated in a network of blood vessels and interstitial fluid.
2 ⁢ ln ⁡ ( 2 ) π ⁢ λ o 2 Δλ = 60 ⁢ ⁢ μ ⁢ ⁢ m ( 18 ) Therefore, the coherence gating implemented with the devices in FIGS. 16 and 17 or other optical sensing devices may be used to determine the absorption characteristics of the glucose in tissue layers no less than 60 μm thick. As illustrated in FIG. 19A, human skin consists of a superficial epidermis layer that is typically 0.1 mm thick. Underneath epidermis is the dermis, approximately 1 mm thick, where glucose concentrates in blood and interstitial fluids. The above analysis indicates that it is possible to use the apparatus shown in FIGS. 16 and 17 to isolate the absorption characteristics of the dermis from that of the epidermis and other layers.
In the above devices for SAM measurements, light beams at different wavelength bands are simultaneously directed by the probe head 220 to the sample 205. Hence, the optical measurements at different wavelengths are performed simultaneously. Alternatively, the optical multiplexer 2520 may be replaced by an optical switch 3010 as shown in FIG. 30 to direct a probe beam within one of the wavelength bands at a time so that probe light beams at different wavelength bands are directed to the sample 205 sequentially at different times to obtain the reflectance maps. In one implementation, the N broad band light sources 2510 can be sequentially linked to the optical device in FIG. 30 through a 1�N optical switch as the switch 3010. The reflective maps, A(λ1), A(λ2) and so on at different wavelength bands are obtained sequentially and are then used in the calculation of SAM.
Δ ⁢ ⁢ z = 2 ⁢ ⁢ ln ⁡ ( 2 ) π ⁢ λ o 2 Δ ⁢ ⁢ λ ( 23 ) For a given bandwidth, Δλ, the depth resolution of the corresponding reflectance map is determined by the above equation. Hence, a broad bandwidth is desirable for resolving a small spatial feature along the direction of the probe beam, which limits the spectral resolution as a tradeoff. For example, if one wants to map an spectral absorbance feature that occupies a 20 nm range near an optical wavelength of 1 μm, light sources of bandwidth around 5 nm can be chosen. Under these conditions, the spatial resolution for SAM is roughly 90 μm.
Assumed Tumor diameter
Approx. Tumor Volume
Optical Power delivered
Estimated Laser Power
5 sec. Exposure
10 sec. Exposure
As an example, Table 1 lists calculated exposure times needed to elevate the temperature of the suspect tissue for different optical power levels delivered to the tissue. The laser power input to the optical delivery waveguide 3332 (e.g., optic fiber) would need to be three times higher assuming 33% coupling efficiency. In the above estimates, it is assume that the malignant tissue behaves thermally as if it were water (about 70% accurate) and that the nodule is essentially in poor thermal contact with the surrounding tissue. Researchers have found that a 10� C. rise in temperature is sufficient to kill cancer cells and that higher temperature rises kill malignant cells more quickly. Base upon the results of Table 1, a 3-6 watt laser should suffice to perform Laser Hyperthermia in-vivo with a 5-10 sec. exposure.
The integrated diagnostic and therapeutic system in FIG. 33 and the technique in FIG. 34 may be implemented to allow both SPN location/detection and bronchoscopic examination to be performed in a single session or visit. In addition, both differential diagnosis and laser therapy can therefore be performed during a single bronchoscopic procedure. Therefore, The three different procedures, SPN detection/location, malignant-benign differential diagnosis, and remedial therapy, can be performed in a single office visit. A CT Scan system may be modified to incorporate the much smaller optical devices for differential diagnosis and laser therapy so that the complete process may be performed on a single piece of equipment. This results in very efficient use of the physician's time and convenience for the patient. Laser therapy methods, such as laser hyperthermia and laser ablation, do not have significant adverse side effects on the patient under treatment and thus are advantageous in this regard in comparison with other therapeutic regimens such as chemotherapy and radiation. In addition, the integrated system in FIG. 34 may be implemented to reduce any delay in the differential diagnosis and therapy and thus such implementation can be advantageous over other methods that use the �wait-and-see� observation of tumor size growth protocol which is often employed to distinguish between malignant and benign SPNs.
Only a few implementations are disclosed in this application. However, it is understood that variations, modifications and enhancements may be made.
Patent CitationsCited PatentFiling datePublication dateApplicantTitleUS4402311Mar 19, 1980Sep 6, 1983Olympus Optical Co., Ltd.Endoscope for medical treatmentUS4848867Sep 22, 1988Jul 18, 1989Hitachi Cable LimitedRotary joint for polarization plane maintaining optical fibersUS4878492Oct 8, 1987Nov 7, 1989C. R. Bard, Inc.Laser balloon catheterUS4991938Apr 7, 1989Feb 12, 1991Gte Laboratories IncorporatedQuasi-achromatic optical isolators and circulators using prisms with total internal fresnel reflectionUS5088493Feb 16, 1988Feb 18, 1992Sclavo, S.P.A.Multiple wavelength light photometer for non-invasive monitoringUS5202745Mar 2, 1992Apr 13, 1993Hewlett-Packard CompanyPolarization independent optical coherence-domain reflectometryUS5321501Apr 29, 1992Jun 14, 1994Massachusetts Institute Of TechnologyMethod and apparatus for optical imaging with means for controlling the longitudinal range of the sampleUS5459570Mar 16, 1993Oct 17, 1995Massachusetts Institute Of TechnologyMethod and apparatus for performing optical measurementsUS5659392Mar 22, 1995Aug 19, 1997Eastman Kodak CompanyAssociated dual interferometric measurement apparatus for determining a physical property of an objectUS5710630Apr 26, 1995Jan 20, 1998Boehringer Mannheim GmbhMethod and apparatus for determining glucose concentration in a biological sampleUS5784162Dec 12, 1995Jul 21, 1998Applied Spectral Imaging Ltd.Spectral bio-imaging methods for biological research, medical diagnostics and therapyUS5803909Oct 6, 1995Sep 8, 1998Hitachi, Ltd.Optical system for measuring metabolism in a body and imaging methodUS5912762Aug 12, 1996Jun 15, 1999Li; LiThin film polarizing deviceUS6034774Jun 26, 1998Mar 7, 2000Eastman Kodak CompanyMethod for determining the retardation of a material using non-coherent light interferometeryUS6134003Feb 27, 1996Oct 17, 2000Massachusetts Institute Of TechnologyMethod and apparatus for performing optical measurements using a fiber optic imaging guidewire, catheter or endoscopeUS6201989Mar 12, 1998Mar 13, 2001Biomax Technologies Inc.Methods and apparatus for detecting the rejection of transplanted tissueUS6219565Feb 5, 1997Apr 17, 2001Diasense, Inc.Methods and apparatus for non-invasive glucose sensing: non-invasive probeUS6246818 *Jun 7, 1999Jun 12, 2001Fujitsu LimitedTunable optical filterUS6252666Mar 31, 2000Jun 26, 2001Optreal Biopsy Technologies, Inc.Method and apparatus for performing optical coherence-domain reflectometry and imaging through a scattering medium employing a power-efficient interferometerUS6282011Jun 26, 2000Aug 28, 2001Massachusetts Institute Of TechnologyGrating based phase control optical delay lineUS6377840Jun 1, 2000Apr 23, 2002Hutchinson Technology IncorporatedSignal acquisition and processing system for reduced output signal drift in a spectrophotometric instrumentUS6421164Jun 13, 2001Jul 16, 2002Massachusetts Institute Of TechnologyInterferometeric imaging with a grating based phase control optical delay lineUS6451009Sep 12, 2000Sep 17, 2002The Regents Of The University Of CaliforniaOCDR guided laser ablation deviceUS6485413Mar 6, 1998Nov 26, 2002The General Hospital CorporationMethods and apparatus for forward-directed optical scanning instrumentsUS6498942Aug 7, 2000Dec 24, 2002The University Of Texas SystemOptoacoustic monitoring of blood oxygenationUS6501551Oct 5, 1999Dec 31, 2002Massachusetts Institute Of TechnologyFiber optic imaging endoscope interferometer with at least one faraday rotatorUS6522407Mar 18, 2002Feb 18, 2003The Regents Of The University Of CaliforniaOptical detection dental disease using polarized lightUS6585639 *Oct 27, 2000Jul 1, 2003PulmonxSheath and method for reconfiguring lung viewing scopeUS6608717Jan 28, 2000Aug 19, 2003Colorado State University Research FoundationOptical coherence microscope and methods of use for rapid in vivo three-dimensional visualization of biological functionUS6609425 *Apr 30, 2001Aug 26, 2003Fuji Photo Film Co., Ltd.Ultrasonic probe and ultrasonic diagnosis apparatus using the sameUS6615072May 21, 1999Sep 2, 2003Olympus Optical Co., Ltd.Optical imaging deviceUS6687010Sep 7, 2000Feb 3, 2004Olympus CorporationRapid depth scanning optical imaging deviceUS6709402Feb 22, 2002Mar 23, 2004Datex-Ohmeda, Inc.Apparatus and method for monitoring respiration with a pulse oximeterUS6725073Jul 17, 2002Apr 20, 2004Board Of Regents, The University Of Texas SystemMethods for noninvasive analyte sensingUS6738144Dec 17, 1999May 18, 2004University Of Central FloridaNon-invasive method and low-coherence apparatus system analysis and process controlUS6753966Mar 9, 2001Jun 22, 2004Textron Systems CorporationOptical probes and methods for spectral analysisUS6847453Nov 5, 2001Jan 25, 2005Optiphase, Inc.All fiber autocorrelatorUS6891984Jul 25, 2002May 10, 2005Lightlab Imaging, LlcScanning miniature optical probes with optical distortion correction and rotational controlUS6901284Feb 18, 2000May 31, 2005Hitachi, Ltd.Optical measuring instrumentUS6903820Jun 4, 2004Jun 7, 2005Tomophase CorporationMeasurements of substances using two different propagation modes of light through a common optical pathUS6903854Apr 18, 2003Jun 7, 2005Imalux CorporationOptical coherence tomography apparatus, optical fiber lateral scanner and a method for studying biological tissues in vivoUS6943881Jun 3, 2004Sep 13, 2005Tomophase CorporationMeasurements of optical inhomogeneity and other properties in substances using propagation modes of lightUS7023563Feb 14, 2003Apr 4, 2006Chian Chiu LiInterferometric optical imaging and storage devicesUS7039454Mar 24, 2000May 2, 2006Hitachi Medical CorporationBiological optical measuring instrumentUS7058155Aug 19, 2004Jun 6, 2006General Electric CompanyMethods and apparatus for detecting structural, perfusion, and functional abnormalitiesUS7207984Aug 4, 2005Apr 24, 2007Cardiofocus, Inc.Methods for projection of energyUS7254429Aug 11, 2004Aug 7, 2007Glucolight CorporationMethod and apparatus for monitoring glucose levels in a biological tissueUS7259851Aug 8, 2005Aug 21, 2007Tomophase CorporationOptical measurements of properties in substances using propagation modes of lightUS7263394Oct 12, 2004Aug 28, 2007Tomophase CorporationCoherence-gated optical glucose monitorUS7428053Oct 9, 2006Sep 23, 2008Imalux CorporationCommon path frequency domain optical coherence reflectometry/tomography deviceUS7456965Aug 21, 2007Nov 25, 2008Tomophase CorporationOptical measurements of properties in substances using propagation modes of lightUS7595879Jun 4, 2004Sep 29, 2009Tomophase CorporationOptically measuring substances using propagation modes of lightUS7831298May 11, 2007Nov 9, 2010Tomophase CorporationMapping physiological functions of tissues in lungs and other organsUS20020049370 *Jul 18, 2001Apr 25, 2002Laufer Michael D.Devices for creating collateral channels in the lungsUS20020126347Mar 7, 2001Sep 12, 2002Hogan Josh N.High data rate multiple wavelength encodingUS20020131049Mar 16, 2001Sep 19, 2002Schmitt Joseph M.Broadband light source system and method thereofUS20030020920Jan 11, 2002Jan 30, 2003Dave Digant P.Method and apparatus for differential phase optical coherence tomographyUS20030114878Dec 14, 2001Jun 19, 2003The Regents Of The University Of CaliforniaCatheter based balloon for therapy modification and positioning of tissueUS20030137669Aug 5, 2002Jul 24, 2003Rollins Andrew M.Aspects of basic OCT engine technologies for high speed optical coherence tomography and light source and other improvements in optical coherence tomographyUS20030187319Mar 25, 2003Oct 2, 2003Olympus Optical Co., Ltd.Sentinel lymph node detecting apparatus, and method thereofUS20040001716Nov 26, 2002Jan 1, 2004Fadi DaouMethods and devices to minimize the optical loss when multiplexing optical signals from a plurality of tunable laser sourcesUS20040140425Jan 6, 2004Jul 22, 2004Olympus CorporationLight scanning probe apparatus using light of low coherenceUS20040218845Apr 9, 2002Nov 4, 2004Wei-Zhong LiDepolarizerUS20040246490Jun 4, 2004Dec 9, 2004Feiling WangMeasurements of substances using two different propagation modes of light through a common optical pathUS20040247268Apr 14, 2004Dec 9, 2004Olympus CorporationOptical imaging systemUS20040258377Oct 30, 2003Dec 23, 2004Berkey George E.Single polarization optical fiber laser and amplifierUS20040260158Jun 17, 2004Dec 23, 2004Hogan Josh N.Non-invasive analysis systemUS20050018202Jun 3, 2004Jan 27, 2005Feiling WangMeasurements of optical inhomogeneity and other properties in substances using propagation modes of lightUS20050053109May 30, 2003Mar 10, 2005Josh HoganIntegrated multiple wavelength systemUS20050075547Oct 12, 2004Apr 7, 2005Feiling WangCoherence-gated optical glucose monitorUS20050286055Aug 8, 2005Dec 29, 2005Feiling WangOptical measurements of properties in substances using propagation modes of lightUS20060089548Oct 19, 2005Apr 27, 2006Hogan Josh NCorrelation of concurrent non-invasively acquired signalsUS20060100490Oct 4, 2005May 11, 2006Feiling WangCross-sectional mapping of spectral absorbance featuresUS20070103683Jun 4, 2004May 10, 2007Feiling WangOptically measuring substances using propagation modes of lightUS20080030740Aug 21, 2007Feb 7, 2008Tomophase CorporationOptical Measurements of Properties in Substances Using Propagation Modes of LightUS20080033300Aug 4, 2006Feb 7, 2008Anh HoangSystems and methods for monitoring temperature during electrosurgery or laser therapyUS20080267562Mar 7, 2008Oct 30, 2008Feiling WangDelivering light via optical waveguide and multi-view optical probe headUS20090073444Nov 25, 2008Mar 19, 2009Tomophase CorporationOptical measurements of properties in substances using propagation modes of lightCN2524241YJan 11, 2002Dec 4, 2002谭玉山Optical fiber biological test instrument by phase tracking methodEP0429297A2Nov 20, 1990May 29, 1991Hamamatsu Photonics K.K.Cancer diagnosis and treatment device having laser beam generatorEP0527050A1Aug 5, 1992Feb 10, 1993Ishikawajima-Harima Jukogyo Kabushiki KaishaCancer therapy systemJP2001066245A Title not availableJP2002013907A Title not availableJP2004317437A Title not availableWO2003062802A2Jan 24, 2003Jul 31, 2003Gen Hospital CorpApparatus and method for rangings and noise reduction of low coherence interferometry lci and optical coherence tomography (oct) signals by parallel detection of spectral bandsWO2005001522A2Jun 4, 2004Jan 6, 2005Tomophase CorpMeasurements of optical inhomogeneity and other properties in substances using propagation modes of lightWO2006041997A2Oct 5, 2005Apr 20, 2006Xiao-Li LiCross-sectional mapping of spectral absorbance featuresWO2006045013A2Oct 20, 2005Apr 27, 2006Tomophase CorpIntegrated disease diagnosis and treatment systemWO2008134449A1Apr 24, 2008Nov 6, 2008Tomophase CorpDelivering light via optical waveguide and multi-view optical probe headWO2009108950A2Mar 2, 2009Sep 3, 2009Tomophase CorporationTemperature profile mapping and guided thermotherapy* Cited by examinerNon-Patent CitationsReference1El-Tonsy, M.H., et al., "Continuous-wave Nd:Yag laser hyperthermia: a successful modality in treatment of basal cell carcinoma," Dermatology Online Journal, 10(2):12 pages, Oct. 2004.2European Search Report dated Nov. 18, 2010 for European Patent Application No. 05813935.3, filed Oct. 20, 2005 (9 pages).3European Search Report dated Nov. 2, 2010 for European Patent Application No. 04754292.3, filed Jun. 4, 2004 (4 pages).4Goldberg, S.N., et al., "Thermal ablation therapy for focal malignancy: a unified approach to underlying principles, techniques, and diagnostic imaging guidance," AJR American Journal Roentgenology, 174(2):323-331, Feb. 2000.5Handbook of Optics, 2nd Edition, vol. 1: Fundamentals, Techniques, & Design, Optical Society of America, McGraw-Hill Professional, pp. 42.68-42.73, Sep. 1994.6International Preliminary Report on Patentability dated Feb. 24, 2009 for PCT/US05/35951 (9 pages).7International Preliminary Report on Patentability dated Nov. 5, 2009 for International Application No. PCT/US2008/061451, filed Apr. 24, 2008 (6 pages).8International Preliminary Report on Patentability for PCT/US04/17649, dated Dec. 22, 2005.9International Search Report and Written Opinion dated Aug. 29, 2008 for PCT/US05/35951 (10 pages).10International Search Report and Written Opinion dated Nov. 20, 2009 for International Application No. PCT/US2009/035773, filed Mar. 2, 2009 (7 pages).11International Search Report and Written Opinion dated Oct. 17, 2008 for PCT/US08/61451 (7 pages).12International Search Report and Written Opinion for PCT/US05/37730, dated Oct. 4, 2007.13James, A., et al., "Airway smooth muscle in health and disease; methods of measurement and relation to function," The European Respiratory Journal, 15(4):782-789, Apr. 2000.14Lucroy, M.D., et al., "Selective laser-induced hyperthermia for the treatment of spontaneous tumors in dogs," Journal of X-Ray Science and Technology, 10(3-4):237-243, (2002).15Miller, J.D., et al., "A Prospective Feasibility Study of Bronchial Thermoplasty in the Human Airway," Chest, 127(6):1999-2006, Jun. 2005.16Nikfarjam, M., et al., "Interstitial laser thermotherapy for liver tumours," British Journal of Surgery, 90(9):1033-1047, Sep. 2003.17Office Action dated Feb. 12, 2010 for Chinese Patent Application No. 200580043930.4 (12 pages).18Office Action dated Mar. 17, 2010 for Japanese Patent Application No. 2006-515173 (4 pages).19Office Action dated Nov. 20, 2009 for Chinese Patent Application No. 200480021343.0 (25 pages).20Office Action dated Oct. 22, 2010 for Canadian Patent Application No. 2,528,417 (3 pages).21Tearney, G., et al., "In Vivo Endoscopic Optical Biopsy with Optical Coherence Tomography," Science, 276(5321):2037-2039, Jun. 1997.22Tumlinson, A., et al., "Endoscope-tip interferometer for ultrahigh resolution frequency domain optical coherence tomography in mouse colon," Optics Express, 14(5):1878-1887, Mar. 2006.23Vakhtin, A.B., et al., "Common-Path Interferometer for Frequency-Domain Optical Coherence Tomography," Applied Optics, 42(34):6953-6958, Dec. 2003.24Yun, S., et al., "Comprehensive volumetric optical microscopy in vivo," Nature Medicine, 12(12):1429-1433, Nov. 2006.25Ziemann, V., et al., "Ideas for an interferometric thermometer," Nuclear Instruments and Methods in Physics Research Section A: Accelerators, Spectrometers, Detectors and Associated Equipment, 564(1):587-589, Aug. 2006.Referenced byCiting PatentFiling datePublication dateApplicantTitleUS20120302828 *Mar 14, 2012Nov 29, 2012Memorial Sloan Kettering Cancer CenterApparatus, system and method for providing laser steering and focusing for incision, excision and ablation of tissue in minimally-invasive surgeryUS20130100442 *May 25, 2012Apr 25, 2013Tomophase CorporationOptical measurements of properties in substances using propagation modes of lightUS20130112858 *Nov 7, 2011May 9, 2013Gooch And Housego PlcPolarization diversity detectorUS20130178706 *Dec 7, 2012Jul 11, 2013Olympus Medical Systems Corp.Scanning endoscope apparatus* Cited by examinerClassifications U.S. Classification600/478, 356/342, 600/473, 356/453, 356/511, 600/476, 600/174International ClassificationA61B6/00Cooperative ClassificationA61B2018/2065, A61B5/0073, A61B5/0084, A61B5/0066, A61B1/00172, A61B5/6852, A61B18/22, A61N5/0601, A61B2017/00057, A61B1/2676, A61B5/0075European ClassificationA61B18/22, A61B1/267D, A61B5/68D1H, A61B5/00P1C, A61B1/00S3Legal EventsDateCodeEventDescriptionOct 2, 2012CCCertificate of correctionJan 3, 2006ASAssignmentOwner name: TOMOPHASE CORPORATION, MASSACHUSETTSFree format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:NORRIS, PETER E.;WANG, FEILING;LI, XIAO-LI;REEL/FRAME:017161/0348;SIGNING DATES FROM 20051015 TO 20051017RotateOriginal ImageGoogle Home - Sitemap - USPTO Bulk Downloads - Privacy Policy - Terms of Service - About Google Patents - Send FeedbackData provided by IFI CLAIMS Patent Services©2012 Google