Integrated system for non-invasive stereotactic radiosurgery with spect / pet 3D targeting for enhanced cancer treatment

Abstract

Disclosed herein is an integrated system for non-invasive stereotactic radiosurgery with SPECT / PET 3D targeting for enhanced cancer treatment. The disclosed integrated system, designed for use in the medical field, is employed in the treatment of various types of cancer. This is applicable in the treatment of all types of solid tumors, including but not limited to, brain, breast, cervix, larynx, lung, pancreas, prostate, skin, spinal cord, stomach, and uterine tumors, as well as soft tissue sarcoma and bone, leukemia, and lymphoma (tumors of the lymphatic system). It is also used in the treatment of some benign tumors. This system provides significant benefits including, but not limited to, integration of imaging and radiotherapy process, no need for stereotactic frames or other methods to determine tumor position in the simulation phase, and not causing stress and anxiety in the patient.

Description

INTEGRATED SYSTEM FOR NON-INVASIVE STEREOTACTIC RADIOSURGERY WITH SPECT / PET 3D TARGETING FOR ENHANCED CANCER TREATMENTTECHNICAL FIELD

[0001] The present disclosure pertains to the field of medical technology, specifically to radiation therapy for cancer treatment. It involves the integration of stereotactic radiosurgery with single-photon emission computed tomography (SPECT) and / or positron emission tomography (PET) for 3D targeting of cancerous tumors. The disclosed system aims to enhance the precision and effectiveness of radiation therapy while improving patient comfort and reducing treatment costs.BACKGROUND ART

[0002] Cancer continues to be a leading cause of death worldwide. The treatment of this pervasive disease often involves the use of radiation therapy, a method that employs high- energy radiation to shrink tumors and kill cancer cells by damaging their DNA. However, traditional radiation therapy methods are associated with several limitations. Traditional radiation therapy may be invasive, causing significant stress and discomfort to the patient. The process may be physically and emotionally taxing, often leading to anxiety and decreased quality of life for the patient. Furthermore, these methods may not be applicable to all types of cancer tumors, limiting their effectiveness.

[0003] Another limitation of traditional radiation therapy is the separation of the diagnostic and treatment processes. The diagnosis of the tumor’s location, dimensions, and extent is often performed by 3D C.T Scan or MRI imaging systems separately from the radiation therapy (commonly known as simulation phase), leading to longer overall treatment times and increased discomfort for the patient. Since the diagnosis of the tumor’s location, dimensions, and extent of the tumor are performed on a separate device from the radiotherapy apparatus, physicians are required to use tools such as stereotactic frames in the Gamma Knife method, temporary or permanent tattoos, elastic meshes, plaster or foam molds to stabilize the patient’s body or organ and mark the location and extent of the tumor. This process can potentially cause significant stress and discomfort for the patient. The accuracy of targeting the tumor and avoiding nearby organs is another critical issue in traditional radiation therapy. Inaccuratetargeting can lead to irradiation of healthy tissues and organs, leading to unnecessary side effects and complications.

[0004] Radiation therapy consists of three different methods: a) External Radiation which is the most common type of radiation therapy. In this method, radiation is emitted from a device located outside the body and is directed towards the cancerous tissue and cells. This process is usually carried out over several weeks, sometimes twice a day for a few weeks. Each session typically lasts 20 to 30 minutes. External radiation therapy is commonly used for outpatient treatment, and patients do not need to be hospitalized. It treats various types of cancer such as breast, bladder, cervical, laryngeal, lung, prostate, and vaginal cancer. Additionally, external radiation therapy is used to alleviate pain or improve other issues when cancer spreads from the primary site to other parts of the body. b) Internal Radiation Therapy or brachytherapy which is a localized method for treating cancer. In brachytherapy, the radiation source is placed inside the tumor tissue or close to it. Sometimes it remains in the body for a while and is then removed. In brachytherapy, the treatment is tumorspecific, and healthy tissues do not receive radiation. Internal radiation therapy can be performed on an outpatient basis or during hospitalization and is used to treat cancers of the head and neck, breast, cervix, prostate, gallbladder, esophagus, eye, lung, etc. This method is often used in conjunction with other treatments such as external radiation therapy, chemotherapy, and surgery. c) Systemic Radiation Therapy. Internal radiation therapy with a liquid source is called systemic radiation therapy. In systemic radiation therapy, a radioactive drug travels through the blood to the cancerous tissues and destroys the cancer cells. This radioactive drug can be administered orally or intravenously. With this method, the patient’s body fluids such as urine, sweat, and saliva have long-term radioactivity. Therefore, special precautions are considered for people who are in contact with the patient. Several factors influence the choice of radiation therapy method including, but not limited to, type of cancer, dimensions of the tumor, location of the tumor in the body, overall health and medical history of the patient, and distance of the cancerous mass from radiation- sensitive healthy tissues.

[0005] The radiation sources used in external radiation therapy include X-rays and gamma rays. These rays are classified as electromagnetic radiation, but their production methods differ. X-rays are produced by a device called Linear Accelerator (LINAC). Low-energy X-rays are used to destroy superficial cancer cells, while high-energy X-rays are used to treat deepertumors. X-rays can irradiate a large area. Gamma rays are emitted from radioisotopes of various elements. Each element’s isotope releases a specific type of radiation with varying energy levels during decay, which affects its penetration depth into the body. Radioactive element isotopes used in radiation therapy include isotopes of cobalt and iridium. Cobalt-60 is the most commonly used isotope in radiation therapy and is a source of gamma radiation with two characteristic energies of 1.33 MeV and 1.77 MeV, and a half-life of over 5 years. This isotope is used in the Gamma Knife radiation therapy device. Cobalt-60 is prepared in rods of various dimensions and is used in medical radiation therapy devices as well as industrial radiography.

[0006] The patient which is treated with radiation therapy should have a unique treatment plan. Due to the variety of radiation methods, treatment design is the first step for treating any patient undergoing radiation therapy. Before treatment, the radiotherapy team may determine the amount and type of radiation. If the patient is to undergo external radiation therapy, the radiotherapist uses a method called Simulation to determine the three-dimensional position of the cancerous tumor. During the Simulation, the patient lies still on the imaging device bed, and the treatment area is determined by the Simulation. During the simulation phase, various imaging methods such as CT scan, MRI, SPECT, or PET are used to help the radiotherapist determine the position and boundaries of the tumor. The areas to be irradiated are marked by permanent or temporary tattoos, metal frames, or elastic polymer meshes installed on the patient’s body. These markers are used to determine the exact location of radiation. Depending on the type of radiation therapy, the radiotherapist may use a mold or other devices to immobilize the patient during treatment. These devices are usually made of foam, plastic, or plaster. In some cases, the radiotherapist uses shields to prevent radiation from penetrating the organs and tissues surrounding the treatment site. Once the simulation is complete, the radiation therapy team may make decisions about the required dose amount, how to deliver it to the desired location, and the treatments that need to be performed for the patient.

[0007] External Radiation Therapy is offered in various methods:1) 3D Conformal Radiation Therapy (3D-CRT): In this type of radiation therapy, Linear Accelerators (LINAC) are used to produce X-rays. The linear accelerator emits electrons at a speed close to the speed of light towards a tungsten target. As a result of the collision of electrons with the tungsten plate, X-rays are produced. The produced X-ray passes through a lead collimator, the shape and dimensions of which are adjusted according to the shape and dimensions of the tumor. The shape and dimensions of the collimator, as well as the intensityof radiation at each stage of treatment, are fixed. The linear accelerator and collimator rotate around the patient in several stages and expose the tumor to X-ray radiation. The tumor is placed at the center of the linear accelerator’s rotation with the help of markers that have been marked on the patient’s body during the Simulation process, by using elastic polymer meshes installed on the patient’s body or by marking Permanent or temporary tattoos. Radiation therapy is usually performed in short sessions, 5 sessions per week for 6 or 7 consecutive weeks. Low doses and intervals between sessions help healthy cells in the treatment area to regenerate. The amount of radiation dose and the number of treatment sessions depend on the size and location of the tumor, the type of tumor, the overall health of the patient, and other factors. 3D-CRT is used to treat tumors that are close to sensitive and vital organs. For example, it can be used to deliver an appropriate dose to head and neck tumors, while the amount of radiation to the spinal cord, optic nerve, salivary glands, and other important organs is much less compared to previous techniques.2) Intensity Modulated Radiation Therapy (IMRT): This method is almost similar to the first one, but the doctor can adjust the intensity and amount of radiation of each beam. In traditional radiotherapies, the treatment was such that the beams irradiated the target surface with a uniform intensity. However, it was possible to some extent, with the help of lead shields or other compensators, to reduce or increase the intensity of the dose in some areas. The goal of the IMRT technique is to treat the patient with radiations with non-uniform effects from different directions, which causes a high dose with high accuracy to reach the target area and a low dose to the surrounding healthy tissues. The treatment design program is such that each beam is divided into a large number of smaller beams, and the desired dose and effect of each of them are defined. In IMRT, the collimator is not in its traditional form and is in the form of MLC (Multi leaf Collimator) and under computer control. MLC allows the radiotherapist to give the desired shape to the radiation beam during different stages of treatment and depending on the angle of radiation of the X-ray to the tumor, instantaneously (On-Line).3) Stereotactic Radiation Therapy (SRT): In this method, one or several beams of X-ray or gamma are used to target cancer tumor cells. The dose of each beam of radiation, alone, is not lethal for cancerous or healthy cells. But the treatment area, which is millimeter- sized, is irradiated from several different angles. Therefore, cancer cells that are at the center of the focal point of radiation receive the highest dose of radiation and their DNA structure is destroyed and their proliferation is prevented. It is also possible that the blood vessels supplying thesecells are also destroyed and lead to their death. This is while the cells around the target area, due to receiving a lower effective dose, may receive much less effect of radiation therapy. Although it is possible that the surrounding areas themselves also contain other cancer cells that may be targeted as the focal point of radiation therapy in later stages. This treatment method is much more accurate than previous methods and causes the least damage to neighboring healthy cells. This method is also known as Stereotactic Radio Surgery (SRS).

[0008] Currently, stereotactic radiation therapy includes two methods, which are performed using two different devices:1) The Gamma Knife device, which is exclusively used for treating brain tumors, uses 201 focused gamma rays that converge at one point for radiation therapy. The gamma ray in this device is supplied by cobalt-60 rods and is emitted towards the target point through special collimators as a narrow beam with a small diameter (about 1 to 3 millimeters). Since the number of beams in this device is very high (210 beams), the radiation dose at the target point is very high, providing the possibility to complete the radiation therapy in just one session in most cases. This advanced technology allows even the deepest parts of the brain, which are inaccessible by conventional surgery, to be treated. Advantages of the Gamma Knife treatment method:• It is an effective method for treating lesions that are not treatable by conventional surgeries.• There is no need to shave the head or open the skull.• In this method, there is no need for anesthesia, and the patient is immune from anesthesi a complic ation s .• There are no post-surgery complications such as infection, adhesion, etc.» The treatment is completed within a few hours, and the patient returns home the same day.• There is no need to go through a convalescence period after the disease.• Accuracy, higher safety, and better results are the advantages of this treatment method compared to conventional surgeries.• It has a much lower cost compared to conventional surgeries.2) The CyberKnife device uses only one high-power X-ray beam. The Linear Accelerator (LINAC) is installed on a robotic arm with six degrees of freedom and can move around thepatient according to the shape and dimensions of the cancerous tumor, and based on the results of three-dimensional images obtained from the simulation process, it can target the tumor with different intensities of radiation from different angles. The accuracy of this device is very high, but due to the use of only one X-ray beam, the treatment may be completed in more than one session (one to five sessions). Although this device is mostly used for treating brain and spinal cord cancerous tumors, some types of CyberKnife devices that have higher power are also used to treat other cancerous tumors such as lymph glands, vertebrae, lungs, breasts, prostate, bones, liver, etc. These devices are technically using the Stereotactic Body Radiation Therapy (SBRT) method or Stereotactic Ablative Radiation Therapy (SART). Recently, new types of CyberKnife devices have been invented that use proton radiation for radiation therapy.

[0009] As discussed above, stereotactic radiosurgery (SRS) is a non-surgical radiation therapy used to treat functional abnormalities and small tumors of the brain. It may deliver precisely- targeted radiation in fewer high-dose treatments than traditional therapy, which can help preserve healthy tissue. In the stereotactic method, a large number of high-energy particle beams (gamma or X-rays) with a low dose, each of which is not harmful to body cells on its own, are irradiated from different directions onto the target point. Although each of these beams alone is not dangerous or harmful for the destruction of the DNA tissue of cancer cells (and of course the healthy tissues around it), the accumulation and concentration of several beams at the target point will increase the radiation dose at that point and will result in the destruction of DNA tissue. However, even with these advanced techniques, there is still a need for improvement. One of the main challenges with SRS is the need for a stereotactic frame. This frame, which is often attached to the patient’s head, is used to ensure precise targeting of the radiation. However, the frame can be uncomfortable for the patient and can add to the invasiveness of the procedure.

[0010] Single-photon emission computed tomography (SPECT) and positron emission tomography (PET) are nuclear medicine imaging techniques that provide 3D information. These techniques can be used to accurately diagnose the location, dimensions, and extent of a cancerous tumor and also metabolic functional of it. So far, the simultaneous combination of these two techniques (determining the position and extent of the tumor and its radiation therapy) has faced technical difficulties and has not been feasible. The present invention aims to address these issues by providing a system for stereotactic radiosurgery with SPECT / PET 3D targeting. This system seeks to eliminate the need for a stereotactic frame, permanent ortemporary tattoos, plaster or foam molds and elastic meshes for fixing and indexing tumor position, size and its extends during simulation and radiosurgery phases; thereby making the procedure less invasive and more comfortable for the patient.

[0011] The goals of this invention are manifold. First and foremost, it aims to provide a completely non-invasive solution for radiation therapy that minimizes patient stress and anxiety, and maximizes comfort and convenience during the treatment process. The invention also aims to offer a comprehensive method for radiation therapy that is applicable to most cancer tumors. This broad applicability may potentially revolutionize the field of radiation therapy.

[0012] Another goal of the invention is to integrate the diagnosis of the tumor’s location, dimensions, and extent (simulation phases) with the radiation therapy process. This integration may lead to a significant reduction in treatment time, thereby increasing patient comfort. The invention also seeks to reduce radiation treatment sessions by enabling stereotactic radiation with a concentrated dose at a very small point, within the dimensions of a sphere with a diameter of one to two and a half millimeters. This precision may lead to more effective treatments and fewer side effects.

[0013] The invention also aims to increase the accuracy of targeting the cancerous tumor and avoid irradiating nearby organs. This may potentially reduce the side effects and complications associated with radiation therapy. The invention also provides the possibility of radiation with a variable dose during an online cancer tumor scan, according to the activity level of tumor cells at that point. This may potentially lead to more personalized and effective treatments.

[0014] Finally, the invention aims to reduce treatment costs, including initial investment, current costs, service and maintenance costs, and other operating costs. This may make the treatment more accessible to a larger number of patients. In summary, this invention represents a significant advancement in the field of radiation therapy. By integrating SPECT / PET 3D targeting and stereotactic radiosurgery, this invention eliminates the need for stereotactic frame, permanent or temporary tattoos, plaster or foam molds and elastic meshes, and it has the potential to greatly improve the treatment of cancerSUMMARY OF THE DISCLOSURE

[0015] This summary is intended to provide an overview of the subject matter of the present disclosure, and is not intended to identify essential elements or key elements of the subjectmatter, nor is it intended to be used to determine the scope of the claimed implementations. The proper scope of the present disclosure may be ascertained from the claims set forth below in view of the detailed description below and the drawings.

[0016] According to one or more exemplary embodiments of the present disclosure, an integrated system for non-invasive stereotactic radiosurgery with SPECT / PET 3D targeting for enhanced cancer treatment is disclosed. In an exemplary embodiment, the integrated system may include a SPECT / PET 3D imaging and stereotactic radiotherapy section, a bed section, and a main control system. In an exemplary embodiment, the SPECT / PET 3D imaging and stereotactic radiotherapy section may include an imaging section and a radiotherapy section.

[0017] In an exemplary embodiment, the SPECT / PET 3D imaging and stereotactic radiotherapy section may include a first base, a second base, a main body, a 3D imaging ring, a plurality of Gamma ray detector modules, two spherical sectors, a plurality of Gamma radiation sources for stereotactic radiation therapy, and a plurality of collimators. In an exemplary embodiment, the main body may be mounted onto the first base and the second base.

[0018] In an exemplary embodiment, the 3D imaging ring may be embedded in the main body. In an exemplary embodiment, the diameter of the 3D imaging ring may be 1200 mm. In an exemplary embodiment, a center of the two spherical sectors and a center of the 3D imaging ring may coincide with each other. In an exemplary embodiment, the plurality of Gamma ray detector modules may be arranged circularly in the 3D imaging ring. In an exemplary embodiment, the two spherical sectors may be embedded in the main body. In an exemplary embodiment, the two spherical sectors may be attached to opposite sides of the 3D imaging ring.

[0019] In an exemplary embodiment, the plurality of Gamma radiation sources may be embedded in the two spherical sectors. In an exemplary embodiment, the plurality of collimators may be embedded in the two spherical sectors. In an exemplary embodiment, each respective collimator from the plurality of collimators may be associated with a respective Gamma radiation source from the plurality of Gamma radiation sources.

[0020] In an exemplary embodiment, the bed section may include a bed, an X-movement mechanism, a Y-movement mechanism, and a Z-movement mechanism. In an exemplary embodiment, the bed may be configured to receive a patient. In an exemplary embodiment, the X-movement mechanism may be configured to move the bed along an X-axis. In an exemplaryembodiment, the Y-movement mechanism may be configured to move the bed along a Y-axis. In an exemplary embodiment, the Y-axis may be perpendicular to the X-axis. In an exemplary embodiment, the Z-movement mechanism may be configured to move the bed along a Z-axis. In an exemplary embodiment, the Z-axis may be perpendicular to the X-axis and the Y-axis surface.

[0021] In an exemplary embodiment, the control system includes a hardware unit for image processing using the SPECT / PET method, a hardware unit for radiation therapy control, and two separate computers. One computer is for imaging and reconstructing three-dimensional images using the SPECT / PET method, and the other computer is for designing the treatment plan, controlling the movements of the bed, and enabling / disabling the gamma ray modules. The hardware image processing unit can process images using the SPECT or PET method or a combination of the two, depending on the type of tumor and the radiopharmaceutical injected into the patient. In an exemplary embodiment, the main control system may be configured to receive reconstructed 3D images from a computer of the imaging section and, based on the received images, automatically and on-line plan and execute the treatment program and direct and position the bed.

[0022] In an exemplary embodiment, the X-movement mechanism may include a rail and timing belt mechanism. In an exemplary embodiment, the X-movement mechanism may further include a first servo motor and a planetary gearbox. In an exemplary embodiment, the servo motor and the planetary gearbox may be connected to the timing belt mechanism. In an exemplary embodiment, the timing belt mechanism may include a timing belt and polarity of timing pulleys. In an exemplary embodiment, the first servo motor may be configured to move the bed along the X-axis.

[0023] In an exemplary embodiment, the Y -movement mechanism may include a rail and a first ball screw mechanism. In an exemplary embodiment, the Y-movement mechanism may include a second servo motor. In an exemplary embodiment, the second servo motor may be connected to the first ball screw mechanism. In an exemplary embodiment, the second servo motor may be configured to move the bed along the Y-axis.

[0024] In an exemplary embodiment, the Z-movement mechanism may include a scissor-like mechanism. In an exemplary embodiment, the Z-movement mechanism may further include a third servo motor, a spiral gearbox, and a second ball screw mechanism. In an exemplary embodiment, the third servo motor, the spiral gearbox, and the second ball screw mechanismconnected to the scissor-like mechanism, the third servo motor configured to move the bed along the Z-axis.

[0025] In an exemplary embodiment, the bed section may further include a manual movement handle. In an exemplary embodiment, the manual movement handle may be attached to the bed. In an exemplary embodiment, the manual movement handle may be configured to move the bed along the X-axis.

[0026] In an exemplary embodiment, the plurality of Gamma ray detector modules may include 90 Gamma ray detector modules. In an exemplary embodiment, a Gamma ray detector module from the plurality of Gamma ray detector modules may include a lead collimator, a scintillation crystal, a frame made of tungsten for installing PIN photodiodes, an array of PIN photodiodes, and circuits for data acquisition and data processing.

[0027] In an exemplary embodiment, a Gamma radiation source from the plurality of Gamma radiation sources may include a fixed body, a source lead shield for the fixed body, a cylindrical rotary lead shield, a source sheath for cylindrical rotary lead shield, a connecting element, a window for Gamma ray emission, a cobalt rod, a servo motor for enabling / disabling the Gamma source, and a cap for the fixed body. In an exemplary embodiment, the fixed body, the source sheath, and the cap may be made of stainless steel. In an exemplary embodiment, the window may be provided on the sheath. In an exemplary embodiment, the cobalt rod may be made of Cobalt 60.

[0028] In an exemplary embodiment, each collimator from the plurality of collimators may include a collimator lead shield, a collimator sheath, and a collimator lock ring. In an exemplary embodiment, the collimator sheath and the lock ring may be made of stainless steel.

[0029] In an exemplary embodiment, the plurality of Gamma radiation sources may include 360 Gamma radiation sources. In an exemplary embodiment, two sets of 180 Gamma radiation sources may be provided on each spherical sector.

[0030] In an exemplary embodiment, the SPECT / PET 3D imaging section may further include an imaging computer. In an exemplary embodiment, the imaging computer may be associated with the plurality of Gamma ray detector modules. In an exemplary embodiment, the imaging computer may be configured to receive the information sent by the plurality of Gamma ray detector modules and according to the radiopharmaceutical injected to the patient, using the SPECT or PET method or a combination of the two, prepare a 3D image in the form of a 3D image matrix. In an exemplary embodiment, a center of the 3D image matrix may coincide thecenter of the proximal spherical sector, the center of the distal spherical sector, and the center of the 3D imaging ring. The output signals and data from the gamma ray detectors are initially processed by a hardware unit for 3D image analysis. The resulting information is then sent to the relevant computer for the reconstruction of three-dimensional images. Depending on the type of cancerous tumor and the radiopharmaceutical injected into the patient, the 3D processing hardware unit can analyze the data received from the gamma ray detectors using either the SPECT or PET method, or a combination of both. The analyzed data is then sent to the image processing computer.

[0031] In an exemplary embodiment, the main control system may be configured to enable a number of the plurality of Gamma radiation sources according to the information obtained from the 3D image matrix, the location of the tumor and the surrounding healthy organs and tissues, as well as the treatment algorithm selected by the radiotherapist and to thereby the necessary therapeutic radiation dose is directed from appropriate angles towards the cancerous tumor cells, leading to their demise.

[0032] In an exemplary embodiment, the main control system may be configured to move the bed in the direction of Cartesian coordinate axes (X, Y, Z), scan and examine the area where the tumor is located and to thereby detect cancerous cells or those susceptible to becoming cancerous.

[0033] In an exemplary embodiment, the main control system may be configured to receive and process the information from the 3D image matrix from the imaging computer at each stage of radiation therapy to find elements containing cancerous cells or those susceptible to becoming cancerous and by issuing necessary commands for the three-axis motion of the bed, place the cancerous cells located in each element at the focal center of the gamma rays from plurality of Gamma radiation sources, and expose them to gamma radiation.

[0034] In an exemplary embodiment, the main control system may be configured to consider the type of cancerous tumor, its location and extent in the patient’s body, and the radiation therapy algorithm chosen by the radiotherapist, issue activation commands to a number of Gamma radiation sources, and allow the elements to be stereotactically irradiated with gamma rays from appropriate directions.

[0035] In an exemplary embodiment, the main control system may be configured to calculate and consider the cumulative dose of received gamma rays in each element which allows theradiation therapy system to apply the appropriate dose to the cancer cells on one hand, and prevent damage to adjacent healthy cells and tissues on the other hand.

[0036] In an exemplary embodiment, the main control system may be configured to personalize and optimize for the radiation therapy of a specific patient based on the default selected treatment program by the radiotherapist, and intelligently update and execute the treatment program with the help of online information obtained from the 3D image matrices.BRIEF DESCRIPTION OF THE DRAWINGS

[0037] The drawing figures depict one or more implementations in accord with the present teachings, by way of example only, not by way of limitation. In the figures, like reference numerals refer to the same or similar elements.

[0038] FIG. 1A illustrates a 3D view of an integrated system for non-invasive stereotactic radiosurgery with SPECT / PET 3D targeting for enhanced cancer treatment, consistent with one or more exemplary embodiments of the present disclosure.

[0039] FIG. IB illustrates a 3D view of an integrated system for non-invasive stereotactic radiosurgery with SPECT / PET 3D targeting for enhanced cancer treatment without any covers, consistent with one or more exemplary embodiments of the present disclosure.

[0040] FIG. 2A illustrates a 3D view of a SPECT / PET 3D imaging and stereotactic radiosurgery section, consistent with one or more exemplary embodiments of the present disclosure.

[0041] FIG. 2B illustrates an exploded view of a SPECT / PET 3D imaging and stereotactic radiosurgery section, consistent with one or more exemplary embodiments of the present disclosure.

[0042] FIG. 3 illustrates a view of a 3D imaging ring, consistent with one or more exemplary embodiments of the present disclosure.

[0043] FIG. 4A illustrates a 3D view of a bed section, consistent with one or more exemplary embodiments of the present disclosure.

[0044] FIG. 4B illustrates a 3D view of a bed section without any covers, consistent with one or more exemplary embodiments of the present disclosure.

[0045] FIG. 5A illustrates a 3D view of a gamma ray detector module from a plurality of Gamma ray detector modules, consistent with one or more exemplary embodiments of the present disclosure.

[0046] FIG. 5B illustrates an exploded view of a gamma ray detector module from a plurality of Gamma ray detector modules, consistent with one or more exemplary embodiments of the present disclosure.

[0047] FIG. 5C illustrates details of a gamma ray detector module from a plurality of Gamma ray detector modules, consistent with one or more exemplary embodiments of the present disclosure.

[0048] FIG. 6A illustrates a 3D view of a Gamma radiation source from a plurality of Gamma radiation sources and a collimator from a plurality of collimators, consistent with one or more exemplary embodiments of the present disclosure. It should be noted that each gamma radiation source consists of two parts: the gamma radiation production source and the collimator. These two parts together form a gamma radiation source. Collimators can vary based on the dimensions of their holes and are considered components that can change as needed. All gamma radiation production sources are identical and remain constant on the external surface of the spherical sectors as long as their cobalt-60 rod has sufficient radiation. If necessary, the cobalt rod is removed from the device and serviced.

[0049] FIG. 6B illustrates an exploded view of a Gamma radiation source from a plurality of Gamma radiation sources and a collimator from a plurality of collimators, consistent with one or more exemplary embodiments of the present disclosure.

[0050] FIG. 6C illustrates details of a Gamma radiation source from a plurality of Gamma radiation sources and a collimator from a plurality of collimators, consistent with one or more exemplary embodiments of the present disclosure.

[0051] FIG. 6D illustrates details of a Gamma radiation source from a plurality of Gamma radiation sources, consistent with one or more exemplary embodiments of the present disclosure.

[0052] FIG. 7 illustrates principles of geometry and computation in the design of collimators for Gamma ray modules, consistent with one or more exemplary embodiments of the present disclosure.

[0053] FIG. 8 illustrates methodology and principles of radiation therapy by using the disclosed integrated system, consistent with one or more exemplary embodiments of the present disclosure.

[0054] FIG. 9 illustrates methodology and principles of radiation therapy by using the disclosed integrated system along with the 3D imaging matrix, consistent with one or more exemplary embodiments of the present disclosure.

[0055] FIG. 10 illustrates a block diagram of the computer / electronic control system of the disclosed integrated system, consistent with one or more exemplary embodiments of the present disclosure.DESCRIPTION OF EMBODIMENTS

[0056] In the following detailed description, numerous specific details are set forth by way of examples in order to provide a thorough understanding of the relevant teachings. However, it should be apparent that the present teachings may be practiced without such details. In other instances, well known methods, procedures, components, and / or circuitry have been described at a relatively high-level, without detail, in order to avoid unnecessarily obscuring aspects of the present teachings.

[0057] The following detailed description is presented to enable a person skilled in the art to make and use the methods and devices disclosed in exemplary embodiments of the present disclosure. For purposes of explanation, specific nomenclature is set forth to provide a thorough understanding of the present disclosure. However, it will be apparent to one skilled in the art that these specific details are not required to practice the disclosed exemplary embodiments. Descriptions of specific exemplary embodiments are provided only as representative examples. Various modifications to the exemplary implementations will be readily apparent to one skilled in the art, and the general principles defined herein may be applied to other implementations and applications without departing from the scope of the present disclosure. The present disclosure is not intended to be limited to the implementations shown, but is to be accorded the widest possible scope consistent with the principles and features disclosed herein.

[0058] Disclosed herein is a device capable of accurately locating and removing cancerous tumors simultaneously. Depending on the type of tumor, an appropriate dose of radiopharmaceuticals is administered intravenously or orally to the patient. These radiopharmaceuticals circulate through the patient’s bloodstream. As cancerous tumor cells require more energy than healthy tissues, they absorb a larger quantity of radiopharmaceuticals, become labeled, and begin to emit gamma rays.

[0059] The disclosed system employs three-dimensional imaging techniques, such as Single Photon Emission Computed Tomography (SPECT), Positron Emission Tomography (PET), or a combination thereof, to pinpoint the exact location of the tumor using gamma rays. The tumor is then targeted with gamma rays emitted from cobalt 60 from various angles using the stereotactic radiation therapy method. This approach aims to destroy the DNA chain of cancer cells and the tissues supplying them with blood, thereby inhibiting their proliferation.

[0060] In this system, 3D imaging and radiation therapy are conducted concurrently within a single device. This eliminates the need for simulation phase includes performing initial MRI, CT scan, or PET Scan imaging prior to the treatment process for locating the position, dimension and extension of tumors, the installation of stereotactic frames on the patient’s body, labeling permanent or temporary tattoos, using plaster or foam molds and elastic meshes for fixing patient body, unlike other radiation therapy methods such as the gamma knife. This system is applicable in the treatment of numerous cancerous tumors that can be labeled by radiopharmaceuticals, including but not limited to, brain, lung, and prostate tumors.

[0061] FIG. 1A shows a 3D view of an integrated system 100 for non-invasive stereotactic radiosurgery with SPECT / PET 3D targeting for enhanced cancer treatment, consistent with one or more exemplary embodiments of the present disclosure. FIG. IB shows a 3D view of integrated system 100 for non-invasive stereotactic radiosurgery with SPECT / PET 3D targeting for enhanced cancer treatment without any cover, consistent with one or more exemplary embodiments of the present disclosure. As shown in FIG. 1A and FIG. IB, in an exemplary embodiment, integrated system 100 may include a SPECT / PET 3D imaging and stereotactic radiosurgery section 101 and a bed section 102.

[0062] In an exemplary embodiment, SPECT / PET 3D imaging and stereotactic radiosurgery section 101 may include a SPECT / PET 3D imaging section in which imaging is performed using Single Photon Emission Computed Tomography (SPECT), or Positron Emission Tomography (PET), or a combination of both. Firstly, it’s important to clarify that the utilization of 3D imaging in this invention diverges slightly from the approaches taken in traditional PET or SPECT imaging systems. Conventional PET or SPECT devices are generally equipped with detectors or gamma cameras that possess a large field of view. The resulting images from these traditional PET or SPECT devices are three-dimensional representations of a specific body part or region. These 3D images can be sliced along the three primary axes of the coordinate system, yielding a series of two-dimensional images that can be interpreted.These images offer valuable insights into the metabolic activity, physical characteristics, and dimensions of various organs or different parts of the body.

[0063] But 3D imaging system in this invention uses small filed gamma camera detectors. The main purpose of the 3D imaging section in this invention is conducting metabolic studies of tumor and providing a very small field image of the tumor. Therefore, its role is to precisely locate the tumor, intelligently guide the radiation therapy section, and autonomously design the treatment program. As such, the imaging section of this system has a limited field of view (Small Field of View). Consequently, the full dimensions and extent of the malignant tumor may not be within the imaging section’s field of view. However, given the role of this section in the overall radiation therapy process, this limitation not only avoids complications but also offers benefits. It’s also worth noting that, over the course of the radiation therapy process, by compiling the small 3D images obtained, it becomes possible to ultimately construct a comprehensive 3D image of the tumor.

[0064] As shown in FIG. 8, The image output from the imaging section takes the form of a compact 3D matrix, or a 3D image matrix. This matrix has approximate dimensions of X: 10.0 mm, Y: 25 mm, and Z: 25 mm. It’s important to note that these dimensions serve as a fundamental basis and can be modified or adjusted as needed in practice. The geometric and three-dimensional center of this rectangular cuboid matrix aligns with the center of the imaging system’s ring. It also corresponds to the center of a sector of the stereotactic radiation therapy sphere, which is the focal point of the gamma rays emitted from the radiation therapy system’s gamma ray modules (also known as the Stereotactic Radiotherapy Focal Point).

[0065] The dimensions of a pixel within this 3D matrix are contingent upon the final resolution of the imaging system. This resolution is influenced by factors such as the geometric properties of the collimators (including shape, dimensions, mesh pitch, mesh wall thickness, and overall collimator thickness), the type and characteristics of the scintillator crystal, and the dimensions, type, and features of the photodiodes (including sensitivity, response speed, and physical dimensions). Other influencing factors include the imaging algorithm and method (whether PET, SPECT, or a combination of both), the data acquisition and image processing system, and the type of radiopharmaceutical used. Based on available data, the best conventional resolution reported for SPECT imaging devices is approximately 0.25 mm, and for PET imaging devices, it’s around 0.75 mm. However, for radiation therapy purposes, a resolution of up to 2.5 mm is deemed sufficient.

[0066] The primary role of the imaging section in this invention is to identify cancerous tumors marked by suitable radiopharmaceuticals, thereby guiding the radiation therapy system. To achieve this, the imaging section continuously provides a 3D matrix of the target area in realtime. Each element of this matrix, in addition to three-dimensional coordinates (X, Y, Z), includes a fourth parameter known as activity (A). This activity parameter indicates the amount of radiopharmaceutical absorption in that element. Given that cancer cells, due to their heightened activity and metabolism, absorb more radiopharmaceuticals, they exhibit a higher activity level than healthy cells. Any element in the 3D matrix with activity exceeding the permissible limit indicates the presence of cancerous cells or cells prone to becoming cancerous. Moreover, the activity level in each cancerous element represents the number of cancer cells within that element. As such, elements with higher activity should receive a higher radiation dose. In the stereotactic method, the radiotherapy dose may be adjusted by altering the number of gamma ray radiation sources and the duration of gamma ray radiation.

[0067] Consequently, the imaging section continuously provides a 3D matrix image, detailing the condition of the cells at the radiation therapy target point (the focal center of the gamma rays emitted from the radiation therapy system’s gamma ray modules) and the surrounding cells in terms of their health or cancerous status to the device’s main control system. This main control system uses this information as a roadmap to direct and guide the stereotactic radiotherapy section. In essence, the main control system of the device may intelligently and automatically design and predict the movement path of the radiotherapy section in subsequent stages based on the information received from the imaging section.

[0068] While the radiopharmaceuticals used in PET and SPECT imaging methods are fundamentally different, and the source of gamma ray production varies, all radiopharmaceuticals ultimately result in gamma ray radiation from the cells of the targeted organ. In SPECT imaging, radiopharmaceuticals such as Technetium-99m, Thallium-201, and Gallium-67 are used. These radiopharmaceuticals emit single -photon gamma rays during nuclear decay, with a half-life ranging from one to several hours.

[0069] In contrast, PET imaging primarily uses fluorodeoxy glucose (FDG) as a radiopharmaceutical. This compound produces a positron during its decay, which upon colliding with an electron, annihilates and emits two gamma ray photons moving at an angle of 180 degrees relative to each other. The half-life of this radiopharmaceutical is relatively short, approximately 110 minutes. For purpose of reference, it should be noted that the energyof the gamma ray photons from each of these radiopharmaceuticals is unique. This characteristic allows gamma ray detectors to identify the source of gamma ray radiation and differentiate between them.

[0070] The imaging section of integrated system 100 comprises approximately 90 gamma ray detector modules. The exact number may vary, but it should always be even. These modules are evenly spaced on the imaging ring. The diameter of the imaging ring should be selected such that, considering a patient of maximum possible dimensions, the focal point of the stereotactic radiation therapy system can reach all parts of their body. Based on experimental tests, measurements, and computer simulations, a diameter of 1200 mm appears to be suitable.

[0071] In an exemplary embodiment, SPECT / PET 3D imaging and stereotactic radiosurgery section 101 may further include a stereotactic radiotherapy section using gamma rays emitted from cobalt 60. In integrated system 100, the stereotactic radiotherapy section employs gamma rays, which are emitted from a Cobalt-60 source. This Cobalt-60 source can be fabricated into bars of varying diameters and lengths. As the most prevalent isotope in radiation therapy, Cobalt-60 serves as the gamma ray radiation source, exhibiting two energy levels of 1.33 MeV and 1.77 MeV. It has a half-life exceeding 5 years, making it a durable choice for therapy. In addition to its medical applications, Cobalt-60 radioactive rods find utility in industrial radiography devices. If required, iridium isotopes may also be incorporated into integrated system 100.

[0072] The employment of Cobalt 60 and gamma rays in radiation therapy presents several advantages over linear accelerators, which generate x-rays of varying energies. The device’s mechanism, including its mechanical, electronic, and control systems, is significantly simpler and more reliable than that of linear accelerators. Also, the initial investment, service, maintenance, and repair costs are substantially lower than those of linear accelerators, making it a more affordable option. Furthermore, it allows for the use of multiple gamma rays in stereotactic radiation therapy, which enhances the dose at the radiation therapy’s focal point and shortens the treatment duration.

[0073] Integrated system 100 incorporates 360 gamma ray modules for stereotactic radiation therapy, although this number can be adjusted as necessary. These modules are distributed across two sectors of a sphere with a diameter of 1200 mm, each sector situated on one side of the imaging ring. Each sector houses 180 gamma ray modules arranged in three rows of 60, with equal angular distance between each module in a row. The gamma ray beam emitted fromeach module intersects precisely at the center of the spherical sector, aligning with the geometric center of the 3D imaging matrix.

[0074] The aforementioned spherical sectors are constructed from aluminum, with an inner diameter of approximately 1200 mm and an outer diameter around 1800 mm. Each sector features 180 apertures to accommodate the installation of the gamma ray modules. The gamma ray source component of each module is positioned in the outer part of the sector, while the collimator component is situated in the inner part. To prevent the leakage of gamma rays in undesired directions, each radiation therapy module is equipped with protective lead shields. A Cobalt 60 rod, housed within a lead shield, can be rotated relative to its fixed outer casing by a small servo motor. This allows the gamma beam output from each module to be enabled / disabled as required by the radiation therapy program.

[0075] With this configuration, the main control system may activate a specific number of gamma ray modules to deliver the necessary dose, based on the 3D images of the cancerous tumor provided by the 3D imaging system, as well as the tumor’s location and the surrounding healthy and sensitive tissues. This may ensure that radiation is directed to the precise point of the cancerous tumor from the most suitable angles.

[0076] FIG. 2A shows a 3D view of SPECT / PET 3D imaging and stereotactic radiosurgery section 101, consistent with one or more exemplary embodiments of the present disclosure. FIG. 2B shows an exploded view of SPECT / PET 3D imaging and stereotactic radiosurgery section 101, consistent with one or more exemplary embodiments of the present disclosure.

[0077] As shown in FIG. 2A and FIG. 2B, in an exemplary embodiment, SPECT / PET 3D imaging and stereotactic radiosurgery section 101 may include a first base 111 and a second base 112. In an exemplary embodiment, SPECT / PET 3D imaging and stereotactic radiosurgery section 101 may further include a main body 113. In an exemplary embodiment, main body 113 may be mounted onto first base 111 and second base 112. In an exemplary embodiment, SPECT / PET 3D imaging and stereotactic radiosurgery section 101 may further include a 3D imaging ring 114. FIG. 3 shows a 3D view of 3D imaging ring 114, consistent with one or more exemplary embodiments of the present disclosure. As shown in FIG. 3, in an exemplary embodiment, 3D imaging ring 114 may be with a plurality of Gamma ray detector modules 115 arranged circularly around 3D imaging ring 114. In an exemplary embodiment, 3D imaging ring 114 may be embedded into main body 113. In an exemplary embodiment, SPECT / PET 3D imaging and stereotactic radiosurgery section 101 may further include twospherical sectors 116 and 117. In an exemplary embodiment, spherical sectors 116 and 117 may be embedded in main body 113. In an exemplary embodiment, spherical sector 116 may be attached to a first side of 3D imaging ring 114. In an exemplary embodiment, the other spherical sector 117 may be attached to a second side of 3D imaging ring 114. In an exemplary embodiment, the center of spherical sectors 116, and 117, and the center of 3D imaging ring 114 may coincide with each other.

[0078] In an exemplary embodiment, SPECT / PET 3D imaging and stereotactic radiosurgery section 101 may further include a plurality of Gamma radiation sources 118 for stereotactic radiation therapy. In an exemplary embodiment, plurality of Gamma radiation sources 118 may be embedded in two spherical sectors 116 and 117. In an exemplary embodiment, SPECT / PET 3D imaging and stereotactic radiosurgery section 101 may further include a plurality of collimators 119. In an exemplary embodiment, plurality of collimators 119 may be embedded in spherical sectors 116 and 117. In an exemplary embodiment, each respective collimator from plurality of collimators 119 may be associated with a respective Gamma radiation source from plurality of Gamma radiation sources 118.

[0079] FIG. 4A shows a 3D view of bed section 102, consistent with one or more exemplary embodiments of the present disclosure. FIG. 4B shows a 3D view of bed section 102 without any cover, consistent with one or more exemplary embodiments of the present disclosure. In an exemplary embodiment, bed 121 may be designed to move along the three coordinate axes (X, Y, Z), enabling it to position the patient at the desired coordinates or move at predetermined speeds. The bed’s surface, where the patient is placed, is constructed from carbon fiber. This material choice ensures maximum mechanical strength, minimal thickness, and consequently, the least absorption, attenuation, and dispersion of gamma rays. This applies to both the gamma rays emitted from the radiopharmaceuticals used for imaging and the gamma rays emitted by the gamma ray modules used for radiation therapy.

[0080] Given that no metal or non-metal parts with a high attenuation coefficient of gamma rays can be situated in the field of view of the imaging or radiation therapy system, the bed’s length is designed such that any part of the patient’s body affected by cancer can be positioned at the center of imaging and radiation therapy. In cases where multiple different parts of the patient’s body are affected by cancer (for instance, in the case of metastasis), it may be necessary to adjust the patient’ s position on the bed and conduct radiation therapy for each part separately. The driving force for each of the moving axes of the bed is supplied by servomotors. These motors ensure maximum accuracy in determining and stabilizing the position, while also enabling smooth and uniform movement at the exact speed determined by the control system.

[0081] The device’s three movement axes can operate simultaneously. The location of each axis is determined by specialized sensors and relayed to the device control system. Additionally, the movement speed of each axis can be individually adjusted and altered. To maintain stability of parts such as the head, hands, or feet, special ergonomic fixtures are employed. These fixtures are installed and secured on the top of the bed.

[0082] The control system includes a hardware unit for image processing using the SPECT / PET method, a hardware unit for radiation therapy control, and two separate computers. One computer is for imaging and reconstructing three-dimensional images using the SPECT / PET method, and the other computer is for designing the treatment plan, controlling the movements of the bed, and enabling / disabling the gamma ray modules. The hardware image processing unit can process images using the SPECT or PET method or a combination of the two, depending on the type of tumor and the radiopharmaceutical injected into the patient. In an exemplary embodiment, integrated system 100 may further include a main control system. The main control system is equipped with an independent and high-speed computer. This system receives three-dimensional reconstructed images from the imaging section’s computer and, based on these images, automatically and online plans and executes the treatment program. The control system is also responsible for guiding and positioning the device’s bed.

[0083] The main control system, considering the received images and according to predetermined algorithms prepared for radiation therapy of each human body organ and member, plans the treatment program. The main control system identifies cancerous elements in each 3D imaging matrix and, based on existing algorithms, decides from which direction and with what dosage of gamma rays to irradiate the tumor. For this purpose, the control system commands the relevant gamma ray modules to activate and proceed with gamma ray radiation. Depending on the extent of the tumor, the control system may use gamma ray modules with collimators of different hole diameters. The main control system, considering the tumor’s position and the sensitive organs and members around it, as well as the activity level of that element from the 3D image matrix located at the focal point of radiation therapy, which indicates the cancerous nature of the cells present in that element, determines the appropriatedosage for radiation therapy. The appropriate dosage is determined by selecting the number of gamma ray modules, the suitable angle, and the necessary duration for radiation.

[0084] As shown in FIG. 4A and FIG. 4B, in an exemplary embodiment, bed section 102 may have three independent movement axes. In an exemplary embodiment, bed section 102 may include a bed 121, an X-movement mechanism 122, a Y-movement mechanism 123, and a Z- movement mechanism 124. In an exemplary embodiment, bed 121 may be configured to receive a patient. In an exemplary embodiment, X-movement mechanism 122 may be configured to move bed 121 along an X-axis 1221. In an exemplary embodiment, X-movement mechanism 122 may include a rail and timing belt mechanism. In an exemplary embodiment, X-movement mechanism 122 may further include a first servo motor 1223 and a planetary gearbox. In an exemplary embodiment, first servo motor 1223 and the planetary gearbox may be connected to the timing belt mechanism. In an exemplary embodiment, first servo motor 1223 may be configured to move bed 121 along X-axis 1221. In an exemplary embodiment, Y-movement mechanism 123 may be configured to move bed 121 along a Y-axis 1231. In an exemplary embodiment, Y -movement mechanism 123 may include a rail and a first ball screw mechanism. In an exemplary embodiment, Y -movement mechanism 123 may further include a second servo motor. In an exemplary embodiment, the second servo motor may be connected to the first ball screw mechanism. In an exemplary embodiment, the second servo motor may be configured to move bed 121 along Y-axis 1231. In an exemplary embodiment, Y-axis 1231 may be perpendicular to X-axis 1221. In an exemplary embodiment, Z-movement mechanism 124 may be configured to move bed 121 along a Z-axis 1241. In an exemplary embodiment, Z-movement mechanism 124 may include a scissor-like mechanism. In an exemplary embodiment, Z-movement mechanism 124 may further include a third servo motor, a spiral gearbox, and a second ball screw mechanism. In an exemplary embodiment, the third servo motor, the spiral gearbox, and the second ball screw mechanism may be connected to the scissor-like mechanism. In an exemplary embodiment, third servo motor 1242 may be configured to move bed 121 along Z-axis 1241. In an exemplary embodiment, Z-axis 1241 may be perpendicular to X-axis 1221 and Y-axis 1231 surface. In an exemplary embodiment, bed section 102 may further include a manual movement handle 125. In an exemplary embodiment, manual movement handle 125 may be attached to bed 121. In an exemplary embodiment, manual movement handle 125 may be configured to move bed 121 along X-axis

[0085] FIG. 5A shows a 3D view of a gamma ray detector module 115 from the plurality of Gamma ray detector modules, consistent with one or more exemplary embodiments of the present disclosure. FIG. 5B shows an exploded view of gamma ray detector module 115 from the plurality of Gamma ray detector modules, consistent with one or more exemplary embodiments of the present disclosure. FIG. 5C shows details of gamma ray detector module 115 from the plurality of Gamma ray detector modules, consistent with one or more exemplary embodiments of the present disclosure. As shown in FIG. 5A and FIG. 5B, in an exemplary embodiment, gamma ray detector module 115 may include a lead collimator 1151, a scintillation crystal 1152, a frame 1153 made of tungsten for installing PIN photodiodes, an array 1154 of PIN photodiodes, and circuits 1155 for data acquisition and data processing.

[0086] In an exemplary embodiment, each gamma ray detector module 115 may employ lead collimators with parallel holes. In an exemplary embodiment, in order to attain the highest resolution, a collimator featuring hexagonal holes with a small diameter (ranging between 1 and 2 mm) may be utilized. For purpose of reference, it should be understood that a smaller diameter of the collimator holes results in a higher image resolution, albeit at the expense of detector sensitivity. In an exemplary embodiment, collimators may measure approximately 41 mm in length, 21 mm in width, and 50 mm in thickness. However, these dimensions may vary depending on the desired resolution and sensitivity.

[0087] Each gamma ray detector module 115 may utilize all types of conventional scintillating crystals used in PET or SPECT imaging devices. One such conventional type is Thallium Doped-Sodium Iodide (NaI[Tl]). However, scintillating crystals with superior sensitivity, efficiency, and quality, such as Cadmium Zinc Telluride (CZT) and Bismuth Germanate (BGO), can also be utilized in the gamma ray modules 115. These recent scintillating crystals exhibit high sensitivity and efficiency, coupled with a rapid time response and excellent linear performance, which has expanded their application in both PET and SPECT imaging methods. The scintillating crystal in this device measures approximately 43 mm in length, 21 mm in width, and 15 mm in thickness. However, these dimensions may vary based on the specific needs and technical specifications of the crystal.

[0088] In an exemplary embodiment, each gamma ray detector module 115 may utilize PIN photodiodes as optical detectors. A PIN photodiode is a type of photodiode that employs a unique structure to enhance its performance. Unlike a simple photodiode, a PIN photodiode features a more complex structure, including a third layer known as the intrinsic or T layer,positioned between the P and N layers. The intrinsic layer serves to control the electric current, thereby increasing and stabilizing the internal area and electric current. This addition improves the PIN photodiode’s performance compared to a simple photodiode.

[0089] These photodiodes are characterized by their high light sensitivity, ultra-fast response time, and very low noise, making them suitable for both PET and SPECT imaging methods. Each gamma ray detector unit can be equipped with either an array of single-pin photodiodes or pre-assembled array modules. If single-pin photodiodes are used, the image resolution may depend on the dimensions of the photodiodes. For instance, photodiodes with a diameter of 5 mm may be used in the presented diagrams. The array created by these photodiodes may include three rows, with two rows containing 6 photodiodes and one row containing 7 photodiodes.

[0090] The PIN photodiodes are housed within a special tungsten frame to protect them from the potentially harmful and disruptive effects of background gamma radiation. While PIN photodiode array modules may be more expensive, their structure, surface unit density of photodiodes, and inclusion of pre -prepared circuits (including a driver, signal processing, and an analog-to-digital converter) provide superior resolution, sensitivity, and signal-to-noise ratio.

[0091] In an exemplary embodiment, each photodiode in gamma ray detector module 115 may be uniquely equipped with a driver circuit, signal processing components, and an analog-to- digital converter, among other features. These circuits serve multiple functions. They detect the optical signals generated by the impact of gamma photons on the scintillating crystal and accurately calculate the impact position. Additionally, they measure the energy of each photon. The measured energy value is then compared with the predefined energy value of the radiation emitted from the radiopharmaceutical. This comparison allows for the separation of the primary rays from the background rays and noise, thereby enhancing the clarity of the resulting image.

[0092] For purpose of reference, it should be noted that in integrated system 100, gamma rays emitted from Cobalt 60 are utilized for radiation therapy. The radiation angle of these rays is designed in such a manner that they do not interfere with the rays produced by the radiopharmaceutical. However, it is possible that a minimal number of Cobalt 60 gamma rays may reach the detectors of the imaging section due to dispersion, reflection, and other factors. The data collection and processing circuits are designed to filter out these rays from theradiation caused by the radiopharmaceutical, based on the energy of Cobalt 60 gamma rays, which have two characteristic energies of 1.33 MeV and 1.77 MeV.

[0093] When a gamma ray photon strikes the scintillating crystal, it generates a flash of light. Depending on its location, this flash may be detected and recorded by several nearby photodiodes. A data processing and analysis system then interprets the signals received from these adjacent photodiodes, which have simultaneously recorded the flash. Using interpolation methods based on the light intensity recorded by each photodiode, the system determines the precise position and time of the gamma ray photon’s impact on the scintillating crystal. This information, which includes the location (X, Y), light intensity (Z), and time of each collision, is then supplied to the 3D image processing and reconstruction unit as the output of each detector unit.

[0094] Integrated system 100 is capable of utilizing either PET or SPECT imaging, or a combination of both, depending on the nature of the cancerous tumor, its location, and other diagnostic parameters. For purpose of reference, it should be noted that that the choice of imaging method dictates the selection of the appropriate radiopharmaceutical.

[0095] For purpose of reference, it should be noted that the combined imaging method (PET- SPECT) is a novel and promising approach introduced for the first time in this invention. This method employs two types of radiopharmaceuticals concurrently, one tailored for PET imaging and the other for SPECT imaging. The superimposition of images derived from both imaging methods may yield more comprehensive and detailed information about the metabolism, dimensions, and spread of a cancerous tumor. While the theoretical application of this method is feasible, its development and practical implementation necessitate further testing and research.

[0096] In conventional SPECT imaging systems, the imaging device is outfitted with one or two gamma cameras. These cameras, through a mechanical mechanism, can rotate around the patient to generate a series of two-dimensional images. The detectors within the cameras capture the single photons of gamma radiation emitted from the patient’s body. This process creates a series of two-dimensional images that represents the distribution of radiation across different parts of the body. Subsequently, these two-dimensional images are processed by the image processing system to construct a 3D image of the relevant body part or organ. For purpose of reference, it should be noted that Gamma cameras, which can rotate around the patient through a mechanical mechanism, stop at specific angles and take a number of two-dimensional images from the patient. For example, if the SPECT system is equipped with two cameras at a relative angle of 90 degrees, during a 90-degree rotation, it takes 32 images at equal relative angles (one image at every 2.8125 degrees). In this way, the number of two- dimensional images obtained from the desired organ will be 64 images. The more images there are, the higher the quality of the reconstructed three-dimensional image will be.

[0097] But in the PET imaging method, the gantry of the device comprises a multitude of gamma ray detectors that are affixed to a ring. For imaging, the patient is required to be positioned within this ring. In this method, the isotope in the radiopharmaceutical decays, emitting positron particles. These positrons combine with electrons, resulting in an annihilation event. This event emits two gamma photons at an angle of 180 degrees. Each photon carries an energy of 511 kilo electron volts. If two photons are simultaneously recorded, or recorded with a time difference of a few nanoseconds, by two opposing detectors, a “true event” is said to have occurred. These two records, which are opposite each other, form a line known as the Line of Response. The collection of these events in the detector illustrates the distribution of the radiopharmaceutical.

[0098] The control system includes an image processing hardware unit for image processing using the SPECT / PET method, a radiotherapy control hardware unit, and two separate computers. One computer is for imaging and reconstructing three-dimensional images using the SPECT / PET method, and the other computer is for designing the treatment plan, controlling the movements of the bed, and enabling / disabling the gamma ray modules. The image processing hardware unit can process images using the SPECT or PET method or a combination of the two, depending on the type of tumor and the radiopharmaceutical injected into the patient. The output signals from the gamma ray detectors are initially processed and interpreted by the image processing hardware unit, and then transferred to the computer for imaging and image processing. The 3D Image Processing & Reconstruction Unit is equipped with an independent, high-speed computer dedicated to receiving information from the 3D image processing unit, processing and reconstructing images, and transmitting 3D images to the radiosurgery control computer. As explained in the previous section, this invention can employ various algorithms for processing and reconstructing 3D images, depending on the type of radiopharmaceutical used and the chosen imaging method:

[0099] 1) SPECT Image Processing and Reconstruction: In this method, two-dimensional images from each gamma ray detector module are processed and analyzed as single photons.Only the location parameters (X, Y) and light intensity (Z) sent from each gamma ray detector module are considered, and the occurrence time parameter (T) does not factor into image processing and reconstruction. Each gamma ray detector module acts as a gamma camera with a small field of view. The presence of 90 gamma ray detectors enables the device to capture images from 90 different angles of a small part of the patient’s body simultaneously where the cancerous tumor is located, and then process and reconstruct the 3D image. The compact size of the gamma ray detector modules allows the image processing and reconstruction unit to provide a new 3D image approximately every few seconds (for example, every 15 seconds).

[0100] 2) PET Image Processing and Reconstruction: In this method, two-dimensional images from each gamma ray detector module are processed and analyzed as photon pairs. The location parameters (X, Y), light intensity (Z), and occurrence time parameter (T) sent from each pair of gamma ray detector modules are considered simultaneously. The information sent from two opposing detectors, which are located at a relative angle of 180 degrees to each other, are compared simultaneously to reveal and record the phenomenon of electron and positron pair annihilation. Each pair of gamma ray detector modules acts as a PET imaging unit with a small field of view. The presence of 90 gamma ray detectors allows the device to observe the phenomenon of electron and positron pair annihilation from 45 different angles simultaneously and then process and reconstruct the 3D image. The compact size of the gamma ray detector modules allows the image processing and reconstruction unit to provide a new 3D image approximately every few seconds (for example, every 15 seconds).

[0101] 3) Image Processing and Reconstruction Using the Combined SPECT-PET Method: In this method, the algorithms described in the previous two parts are used alternately. In each cycle, an image is created from one of the aforementioned methods, and the image processing and reconstruction unit combines the two to create an image from the two methods.

[0102] FIG. 6A shows a 3D view of Gamma radiation source 118a from plurality of Gamma radiation sources 118 and a collimator 119a from plurality of collimators 119, consistent with one or more exemplary embodiments of the present disclosure. FIG. 6B shows an exploded view of Gamma radiation source 118a from plurality of Gamma radiation sources 118 and collimator 119a from plurality of collimators 119, consistent with one or more exemplary embodiments of the present disclosure. FIG. 6C shows details of Gamma radiation source 118a from plurality of Gamma radiation sources 118 and collimator 119a from plurality of collimators 119, consistent with one or more exemplary embodiments of the present disclosure.FIG. 6D shows details of Gamma radiation source 118a from plurality of Gamma radiation sources 118, consistent with one or more exemplary embodiments of the present disclosure.

[0103] As shown in FIG. 6A and FIG. 6B, in an exemplary embodiment, collimator 119a may include a collimator lead shield 1191, a collimator sheath 1192, and a lock ring 1193. In an exemplary embodiment, collimator sheath 1191 and lock ring 1193 may be made of stainless steel. Collimator sheath 1192 is a metal shell with a thickness of 3 mm made of stainless steel, inside which collimator lead shield 1191 is located. Collimator lead shield 1191 is placed inside collimator sheath 1192 and has a longitudinal hole with a specific diameter. FIG. 7 shows principles of geometry and computation in the design of collimators for Gamma ray modules, consistent with one or more exemplary embodiments of the present disclosure. The length (1) and diameter (d) of this hole, along with the distance from the target point to the collimator exit hole (L), determines the diameter under radiation at the target point (D). For example, with a collimator with a hole diameter of 0.5 mm (d) and a length of 300 mm (1), at a distance of 600 mm (L) from the exit of the collimator, the maximum diameter of the radiation area will be equivalent to 2.5 mm (D):Z / 2 _ L + l / 2 ~d ~ D• d: Diameter of the collimator hole (mm)• D: Diameter of the radiation area at the target point (mm)• 1: Length of the collimator (mm)• L: Distance from the target point to the collimator exit hole (mm)

[0104] As per requirements, collimators with varying specifications can be designed and manufactured for radiation therapy. This invention utilizes collimators of uniform length (1 = 300 mm), but with holes of different diameters. These collimators are available in three different sizes, with radiation area diameters of 2.5 mm, 4 mm, and 6 mm. Typically, on the radiation therapy device of the present disclosure, a certain number of collimators of each different size are installed. On average, one could select approximately 60% of the collimators from the 2.5 mm size, 20% from the 4 mm size, and the remaining 20% from the 6 mm size. However, these percentages are entirely adjustable based on needs. Considering the 3D images obtained from the imaging section, the main control system for executing stereotactic radiation therapy selectsan array of collimators with a suitable radiation area diameter. This ensures the most effective radiation therapy outcome, delivering the maximum dose to cancer cells and the minimum dose to the surrounding healthy cells.

[0105] Lock ring 1193 is made integrally with the collimator sheath and is made of stainless steel. Collimators are movable parts that can be replaced or their installation location can be changed on the spherical sectors of the radiation therapy section of integrated system 100. This steel ring is used as a handle to remove the collimators from their place or to insert and lock them in the desired position.

[0106] Cobalt 60 rod emits gamma rays in all directions like a light bulb. The collimator has the task of parallelizing the gamma rays coming out of the cobalt 60 rod and guiding them towards the focal point of stereotactic radiation therapy. In other words, by removing nonparallel rays, the collimator allows parallel and parallel rays to pass. By changing two parameters, the diameter of the collimator lead shield hole and its length, it is possible to adjust the diameter of the radiation circle of gamma rays in a certain distance. Collimators, tailored to specific needs, can be designed and manufactured for radiation therapy. In integrated system 100, collimators of identical length (1 = 300 mm), but with varying hole diameters are utilized. These collimators come in three sizes, with radiation area diameters of 2.5 mm, 4 mm, and 6 mm. Typically, a variety of collimator sizes are installed on the radiation therapy device. On average, about 60% of the collimators can be chosen from the 2.5 mm size, 20% from the 4 mm size, and another 20% from the 6 mm size. However, these percentages can be fully adjusted according to needs. Based on the 3D images procured from the imaging unit, the main control system for the execution of stereotactic radiation therapy selects an array of collimators with the diameter of the suitable radiation area. This is done to achieve the most effective radiation therapy result, with the maximum dose for cancer cells and the minimum dose for surrounding healthy cells.

[0107] In an exemplary embodiment, Gamma radiation source 118a may include a fixed body 1181, a source lead shield 1182 for fixed body 1181, a cylindrical rotary lead shield 1183, a source sheath 1184 for cylindrical rotary lead shield 1183, a connecting element 1185, a window 1186 for Gamma ray emission, a cobalt rod 1187, a servo motor 1188 for enabling / disabling the Gamma ray, and a cap 1189 for fixed body 1181. In an exemplary embodiment, source sheath 1184 may be made of stainless steel. In an exemplary embodiment, connecting element 1185 may be configured to receive a collimator from plurality of collimators 119. In an exemplaryembodiment, window 1186 may be provided on the source lead shield 1182 and source sheath 1184. In an exemplary embodiment, cobalt rod 1187 may be made of Cobalt 60. In an exemplary embodiment, cap 1188 may be made of stainless steel.

[0108] In an exemplary embodiment, cobalt rods may be placed inside a cylindrical lead sheath. This sheath has a shell made of stainless steel with a thickness of 3 mm, the empty space of which is completely filled with lead. This lead sheath prevents the leakage of gamma rays from unwanted directions. The mentioned lead sheath is connected from one of its bases to the servo motor for enabling / disabling the gamma ray and it can rotate 90 degrees around its longitudinal axis.

[0109] In an exemplary embodiment, connecting element 1185 may be actually a part of the shell of the fixed body of the gamma ray source and its material is made of stainless steel, in which the head of the collimator is placed and fixed. Window 1186 is also a part of the shell of the fixed body of the gamma ray source and its lead shield, through which the gamma rays produced by the cobalt 60 rod can be sent to the collimator and from there to the cancerous tumor. Cobalt 60 rods, available in various diameters and lengths, are manufactured and supplied by the respective producers and have a half-life of 5 years. In the context of this invention, the Cobalt 60 rods have a diameter of 6 mm and a length of 12 mm. However, these specified dimensions are subject to variation. The gamma ray source servo motor is affixed to the body, its shaft linked with a rotating lead shield sheath and a cobalt rod. This servo motor is governed by a square pulse. In essence, the primary control system can control the rotation angle of the servo motor’s output shaft using the Pulse Width Modulation (PWM) technique. As a result, with the rotation of the lead shield casing and the cobalt rod, the cobalt-60 rod is positioned in front of the gamma ray exit window, and the module begins to emit gamma rays. Also, when there is no need for gamma radiation, by rotating the lead shield casing and the cobalt rod, the cobalt-60 rod moves away from the gamma ray exit window, and the gamma ray emission is cut off.

[0110] FIG. 8 shows methodology and principles of radiation therapy by using integrated system 100, consistent with one or more exemplary embodiments of the present disclosure. FIG. 9 shows methodology and principles of radiation therapy by using integrated system 100 along with the 3D imaging matrix, consistent with one or more exemplary embodiments of the present disclosure. FIG. 10 shows a block diagram of a computer / electronic control system of integrated system 100, consistent with one or more exemplary embodiments of the present disclosure.

[0111] In order to use the disclosed system, the radiotherapist determines the approximate location of the tumor or cancerous tumors based on previous diagnostic imaging, which may have been prepared using CT scan, MRI, PET, or SPECT methods. Depending on the type of tumor intended for radiation therapy, the appropriate radiopharmaceutical is injected into the patient and they wait for the radiopharmaceutical to be absorbed by the cancerous tumor cells. This period may vary depending on the type of radiopharmaceutical. Then, the patient lies on the radiation therapy system bed and is placed in the appropriate position and location for radiation therapy by the radiotherapist. Depending on the position and type of tumor, the patient may be placed on the bed in a supine or prone position.

[0112] If necessary, the radiotherapist may use auxiliary tools and fixtures that have been designed and built for this purpose, and fix the part of the patient’s body where the tumor is located. However, given the method of operation of this device, there is no need to completely immobilize the patient’s body, and the radiotherapist tries to ensure that the patient is completely relaxed in terms of positioning on the bed and psychological issues, and does not impose any stress or anxiety on them.

[0113] Then, the radiotherapist guides the patient towards the radiation therapy section with the help of the three axes movement of the bed, and tries to place it in the center of the radiation therapy ring, considering the approximate location of the cancerous tumor. Then, the radiotherapist leaves the radiation therapy room and issues the command to start radiation therapy from the control room.

[0114] Before starting the radiation therapy process, and considering the type of radiopharmaceutical used, they may determine and adjust the imaging system protocol (SPECT / PET or hybrid). They must also select one of the appropriate treatment programs, considering the type of cancerous tumor and its location in the patient’ s body. These treatment programs are predefined on the device control system software and can have variety and adjustable parameters that can be personalized for each patient. In each treatment program, considering the type of tumor, its location, and the sensitive organs and tissues around it, the appropriate angles of stereotactic radiation therapy and other related parameters may be predetermined and adjusted.

[0115] With the start of the radiation therapy process, the imaging system starts working according to the selected protocol (SPECT I PET or hybrid), and the 3D imaging section’s computer creates a small 3D image in the form of a 3D matrix (for example, every 15 seconds),which has been previously explained. This 3D image is sent to the radiation therapy computer after being completed and processed.

[0116] The radiation therapy computer reprocesses and examines each 3D image matrix. If in the current position of the bed and in the center of the 3D image matrix, an activity higher than the normal level is detected, which indicates the presence of cancer cells in that element, the radiation therapy control computer, considering the pre-selected program and the activity level of that element, may enable specific gamma ray modules to irradiate gamma rays. In the method of stereotactic radiation therapy, the dose irradiated from each gamma ray module alone is not lethal for either cancer cells or healthy cells. However, the accumulation of several gamma ray beams that reinforce each other in the center of the radiation therapy ring creates a high and lethal dose for the cancer cells located in that part, which may lead to the destruction of the DNA strands of cancer cells and their death. If the elements adjacent to the central element in the image matrix also have a high activity, the radiation therapy control system may use gamma ray modules with a larger radiation area diameter to be able to irradiate a larger volume of the tumor at a single time and thus reduce the duration of radiation therapy.

[0117] But if none of the elements present in the 3D image matrix contain cancer cells, or the central element does not contain cancer cells but other elements in that matrix are diagnosed as cancerous, the radiation therapy control system, by moving the bed in the appropriate directions, may find the cancer cells, place them in the focal center of the gamma ray modules, and carry out the radiation therapy process. In fact, the radiation therapy control system, by moving the bed in its three axes, scans the area where the radiotherapist has approximately diagnosed the location of the tumor, and by finding the cancer cells and considering the pre-determined treatment program, may automatically perform the radiation therapy process.

[0118] The scanning process to find cancer cells in this invention can be somewhat similar to the process of making parts in 3D printers. The control system scans the specified area layer by layer and if it finds cancer cells or cells prone to becoming cancerous, it targets them with lethal doses of gamma rays. This is while other radiation therapy methods, solely through the information obtained from the simulation phase, try to find the approximate location of the tumor relative to the existing signs and references, and assuming that the targeting has been done correctly, proceed to perform the radiation therapy process.

[0119] In this way, since in this invention finding cancer cells is done continuously and with simultaneous imaging with radiation therapy, if the patient moves slightly due to fatigue, stress,etc., or makes a small movement, this may be detected in the 3D images taken, and the radiation therapy control system may automatically make the necessary corrections to compensate for it. Therefore, in the system of this invention, there is no need for a stereotactic frame and other harsh and stressful methods to determine the location of the tumor, and the patient may be treated with comfort, peace, and minimal stress.

[0120] With the gradual completion of the radiation therapy process and the complete scan of the area suspected of having a cancerous tumor, the imaging system may provide a precise 3D image of the shape and texture of the cancerous tumor that has been under radiation therapy. This information may be used to examine the course of treatment and the effectiveness of the radiation therapy process in later stages of treatment.

[0121] The control system in the radiation therapy system also calculates and considers the cumulative dose of gamma rays received in each element. For example, an element that is not located in the center of the 3D image matrix may be in the path of a gamma ray beam and receive an ineffective dose at one stage of radiation therapy. It is possible that the same element, again in the radiation therapy of another cancerous element, is again in the path of another gamma ray beam and receives another ineffective dose. The device control system, having the three- dimensional coordinates of the area under radiation therapy and considering the treatment program executed, is able to calculate the cumulative dose of each of the elements located in the radiation therapy area. This information helps the radiation therapy control system to apply the appropriate dose to cancer cells and prevent damage to neighboring healthy cells and tissues.

[0122] As discussed above, using integrated system 100 may provide significant benefits. In this system, the process of detecting the position, dimensions, and extent of the tumor is carried out simultaneously with the radiation therapy process. Therefore, there is no need to install a stereotactic frame or other similar auxiliary equipment to determine the position, dimensions, and extent of the tumor on the patient’s body. As a result, treatment by this device brings the least stress and anxiety for the patient, providing them with comfort and ease throughout the treatment stages. Furthermore, this invention presents a comprehensive method for treating most cancerous tumors that can be marked by radiopharmaceuticals. Furthermore, the integration of the process of detecting the position, dimensions, and extent of the tumor, in conjunction with the radiation therapy process in this invention, leads to a reduction in treatment time. It simplifies the treatment process for the patient and provides them with greater comfort.

[0123] Furthermore, the use of stereotactic radiation therapy in this invention, with a concentrated dose in a very small point within the dimensions of a sphere with a diameter of one to 2.5 millimeters, results in a reduction of radiation therapy sessions. Furthermore, the integration of the process of detecting the position, dimensions, and extent of the tumor with the radiation therapy process in this invention, enhances the precision of targeting the cancerous tumor and avoids irradiating adjacent organs and tissues. Furthermore, in this system, each of the gamma ray radiation sources can be enabled / disabled under the command of the control system. This allows for the possibility of irradiation with a variable dose during the scanning of the cancerous tumor, online and proportional to the activity level of the tumor at that point.

[0124] Furthermore, the costs of treatment, initial investment, ongoing costs, service and maintenance fees, and even operator costs in the disclosed device are significantly reduced due to the integration of the process of detecting the position, dimensions, and extent of the tumor with the radiation therapy process and the simplification of the device’s operating mechanism. Furthermore, given the integration of the process of detecting the position, dimensions, and extent of the tumor with the radiation therapy process, the possibility of designing an automatic and intelligent treatment program online based on the results of simultaneous imaging of the cancerous tumor in this device has been facilitated. Furthermore, with regard to the method of operation of the disclosed device, human errors resulting from incorrect, inaccurate, and unprincipled treatment program design may be greatly reduced.

[0125] Furthermore, since the radiation therapy section in this invention has a very large internal diameter (about 1200 millimeters), patients who suffer from fear of small and enclosed spaces (Claustrophobia) will not experience fear and anxiety during treatment with this device. Furthermore, the disclosed system uses gamma rays for radiation therapy, which compared to radiation therapy devices that use X-rays, has more energy and penetrating power. Therefore, this makes it possible to use this system for the treatment of most cancerous tumors in all different parts of the body, even tumors that are located deep relative to the body surface. This is while the Gamma Knife device can only be used for the treatment of brain tumors and the head and neck area.

[0126] While the foregoing has described what may be considered to be the best mode and / or other examples, it is understood that various modifications may be made therein and that the subject matter disclosed herein may be implemented in various forms and examples, and that the teachings may be applied in numerous applications, only some of which have been describedherein. It is intended by the following claims to claim any and all applications, modifications and variations that fall within the true scope of the present teachings.

[0127] Unless otherwise stated, all measurements, values, ratings, positions, magnitudes, sizes, and other specifications that are set forth in this specification, including in the claims that follow, are approximate, not exact. They are intended to have a reasonable range that is consistent with the functions to which they relate and with what is customary in the art to which they pertain.

[0128] The scope of protection is limited solely by the claims that now follow. That scope is intended and should be interpreted to be as broad as is consistent with the ordinary meaning of the language that is used in the claims when interpreted in light of this specification and the prosecution history that follows and to encompass all structural and functional equivalents. Notwithstanding, none of the claims are intended to embrace subject matter that fails to satisfy the requirement of Sections 101, 102, or 103 of the Patent Act, nor should they be interpreted in such a way. Any unintended embracement of such subject matter is hereby disclaimed.

[0129] Except as stated immediately above, nothing that has been stated or illustrated is intended or should be interpreted to cause a dedication of any component, step, feature, object, benefit, advantage, or equivalent to the public, regardless of whether it is or is not recited in the claims.

[0130] It will be understood that the terms and expressions used herein have the ordinary meaning as is accorded to such terms and expressions with respect to their corresponding respective spaces of inquiry and study except where specific meanings have otherwise been set forth herein. Relational terms such as first and second and the like may be used solely to distinguish one entity or action from another without necessarily requiring or implying any actual such relationship or order between such entities or actions. The terms “comprises,” “comprising,” or any other variation thereof, are intended to cover a non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements does not include only those elements but may include other elements not expressly listed or inherent to such process, method, article, or apparatus. An element proceeded by “a” or “an” does not, without further constraints, preclude the existence of additional identical elements in the process, method, article, or apparatus that comprises the element.

[0131] The Abstract of the Disclosure is provided to allow the reader to quickly ascertain the nature of the technical disclosure. It is submitted with the understanding that it will not be used to interpret or limit the scope or meaning of the claims. In addition, in the foregoing DetailedDescription, it can be seen that various features are grouped together in various implementations. This is for purposes of streamlining the disclosure, and is not to be interpreted as reflecting an intention that the claimed implementations require more features than are expressly recited in each claim. Rather, as the following claims reflect, inventive subject matter lies in less than all features of a single disclosed implementation. Thus, the following claims are hereby incorporated into the Detailed Description, with each claim standing on its own as a separately claimed subject matter.

[0132] While various implementations have been described, the description is intended to be exemplary, rather than limiting and it will be apparent to those of ordinary skill in the art that many more implementations are possible that are within the scope of the implementations.Although many possible combinations of features are shown in the accompanying figures and discussed in this detailed description, many other combinations of the disclosed features are possible. Any feature of any implementation may be used in combination with or substituted for any other feature or element in any other implementation unless specifically restricted. Therefore, it will be understood that any of the features shown and / or discussed in the present disclosure may be implemented together in any suitable combination. Accordingly, the implementations are not to be restricted except in light of the attached claims and their equivalents. Also, various modifications and changes may be made within the scope of the attached claims.

Claims

What is claimed is:1 - An integrated system for non-invasive stereotactic radiosurgery with SPECT / PET 3D targeting for enhanced cancer treatment, the integrated system comprising: a SPECT / PET 3D imaging and stereotactic radiotherapy section, the SPECT / PET 3D imaging and stereotactic radiotherapy section comprising an imaging section and a radiotherapy section, the SPECT / PET 3D imaging and stereotactic radiotherapy section comprises: a first base; a second base; a main body, the main body mounted onto the first base and the second base; a 3D imaging ring, the 3D imaging ring embedded in the main body; a plurality of Gamma ray detector modules, the plurality of Gamma ray detector modules arranged circularly around the 3D imaging ring;Two spherical sectors, the two spherical sectors embedded in the main body, the two spherical sectors attached to opposite sides of the 3D imaging ring; a plurality of Gamma radiation sources for stereotactic radiation therapy, the plurality of Gamma radiation sources embedded in the two spherical sectors; a plurality of collimators, the plurality of collimators embedded in the two spherical sectors, each respective collimator from the plurality of collimators associated with a respective Gamma radiation source from the plurality of Gamma radiation sources; a bed section with three independent movement axes, the bed section comprising:a bed, the bed configured to receive a patient; an X-movement mechanism, the X-movement mechanism configured to move the bed along an X-axis; a Y-movement mechanism, the Y-movement mechanism configured to move the bed along a Y-axis, the Y-axis perpendicular to the X-axis; and a Z-movement mechanism, the Z-movement mechanism configured to move the bed along a Z-axis, the Z-axis perpendicular to the X-axis and the Y-axis; and a main control system, the main control system configured to: receive reconstructed 3D images from a computer of the imaging section and, based on the received images, automatically and on-line plan and execute the treatment program; and direct and position the bed.2- The integrated system of claim 1 , wherein the X-movement mechanism comprises a rail and timing belt mechanism.3- The integrated system of claim 2, wherein the X-movement mechanism further comprises a first servo motor and a planetary gearbox, the servo motor and the planetary gearbox connected to the timing belt mechanism, the first servo motor configured to move the bed along the X- axis.4- The integrated system of claim 3, wherein the Y-movement mechanism comprises a rail and a first ball screw mechanism.5- The integrated system of claim 4, wherein the Y-movement mechanism comprises a second servo motor, the second servo motor connected to the rail and the first ball screw mechanism, the second servo motor configured to move the bed along the Y-axis.6- The integrated system of claim 5, wherein the Z-movement mechanism comprises a scissor- like mechanism.7- The integrated system of claim 6, wherein the Z-movement mechanism further comprises a third servo motor, a spiral gearbox, and a second ball screw mechanism, the third servo motor, the spiral gearbox, and the second ball screw mechanism connected to the scissor-like mechanism, the third servo motor configured to move the bed along the Z-axis.8- The integrated system of claim 7, wherein the bed section further comprises a manual movement handle, the manual movement handle attached to the bed, the manual movement handle configured to move the bed along the X-axis.9- The integrated system of claim 8, wherein a Gamma ray detector module from the plurality of Gamma ray detector modules comprises: a lead collimator; a scintillation crystal; a frame for installing PIN photodiodes, the frame made of tungsten;an array of PIN photodiodes; and circuits for data acquisition and data processing.10- The integrated system of claim 9, wherein a Gamma radiation source from the plurality of Gamma radiation sources comprises: a fixed body, the fixed body made of stainless steel; a source lead shield for the fixed body; a cylindrical rotary lead shield; a source sheath for cylindrical rotary lead shield, the source sheath made of stainless steel; a connecting element, the connecting element configured to receive a collimator from the plurality of collimators, the connecting element made of stainless steel; a window for Gamma ray emission, the window provided on the cylindrical rotary lead shield and its sheath and also lead shield for the fixed body; a cobalt rod, the cobalt rod made of Cobalt 60; a servo motor for enabling / disabling the Gamma ray; and a cap for the fixed body, the cap made of stainless steel.11- The integrated system of claim 10, wherein each collimator from the plurality of collimators comprises: a collimator lead shield; a collimator sheath, the collimator sheath made of stainless steel; and a lock ring, the lock ring made of stainless steel.12- The integrated system of claim 11. wherein the plurality of Gamma ray detector modules comprises 90 Gamma ray detector modules.13- The integrated system of claim 12, wherein the plurality of Gamma radiation sources comprises 360 Gamma radiation sources, 180 Gamma radiation sources provided on the each spherical sector.14- The integrated system of claim 13, wherein a diameter of the 3D imaging ring is 1200 mm.15- The integrated system of claim 14, wherein a center of the spherical sectors and a center of the 3D imaging ring coincide with each other.16- The integrated system of claim 15, wherein the main control system comprises: an image processing hardware unit for Image processing by SPECT / PET method, the image processing hardware unit comprising a PET coincidence processing unit and a SPECT processing unit; a radiosurgery hardware unit, the radiosurgery hardware unit comprising a bed 3D motion control unit and a stereotactic Gamma ray modules control processing unit; and two separate computers, the two separate computers comprising: an image processing computer for imaging and reconstructing three-dimensional images using the SPECT / PET method; anda radiosurgery control computer for designing the treatment plan, controlling the movements of the bed, and enabling / disabling the gamma ray modules.17- The integrated system of claim 16, wherein the image processing hardware unit is configured to process images using the SPECT or PET method or a combination of the two, depending on the type of tumor and the radiopharmaceutical injected into the patient; and the output signals from the gamma ray detectors are initially processed and interpreted by the hardware unit of the image processing, and then transferred to the computer for imaging and image processing;18- The integrated system of claim 17, wherein the SPECT / PET 3D imaging and stereotactic radiotherapy section further comprises an imaging computer, the imaging computer associated with the plurality of Gamma ray detector modules, the imaging computer configured to receive the information sent by the plurality of Gamma ray detector modules and according to the radiopharmaceutical injected to the patient, using the SPECT or PET method or a combination of the two, prepare a 3D image in the form of a 3D image matrix.19- The integrated system of claim 18, wherein a center of the 3D image matrix coincides the center of the two spherical sectors and the center of the 3D imaging ring.20- The integrated system of claim 19, wherein the main control system is configured to: turn on a number of the plurality of Gamma radiation sources according to the information obtained from the 3D image matrix, the location of the tumor and the surrounding healthy organs and tissues, as well as the treatment algorithm selected by the radiotherapistand to thereby the necessary therapeutic radiation dose is directed from appropriate angles towards the cancerous tumor cells, leading to their demise; move the bed in the direction of Cartesian coordinate axes (X, Y, Z), scan and examine the area where the tumor is located and to thereby detect cancerous cells or those susceptible to becoming cancerous; receive and process the information from the 3D image matrix from the imaging computer at each stage of radiation therapy to find elements containing cancerous cells or those susceptible to becoming cancerous and by issuing necessary commands for the three-axis motion of the bed, place the cancerous cells located in each element at the focal center of the gamma rays from plurality of Gamma radiation sources, and expose them to gamma radiation; consider the type of cancerous tumor, its location and extent in the patient’s body, and the radiation therapy algorithm chosen by the radiotherapist, issue activation commands to a number of Gamma radiation sources, and allow the elements to be stereotactically irradiated with gamma rays from appropriate directions; calculate and consider the cumulative dose of received gamma rays in each element which allows the radiation therapy system to apply the appropriate dose to the cancer cells on one hand, and prevent damage to adjacent healthy cells and tissues on the other hand; and personalize and optimize for the radiation therapy of a specific patient based on the default selected treatment program by the radiotherapist, and intelligently update and execute the treatment program with the help of online information obtained from the 3D image matrices.

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