Abstract:
Apparatus for performing electron radiation therapy on a breast cancer patient preferably includes an intraoperative electron radiation therapy machine, an intraoperative electron radiation therapy collimator tube connected to the intraoperative electron radiation therapy machine, and a plurality of filters made of a material having substantially the same density as human breast tissue for placement between the machine and the patient to change the energy of a monoenergetic beam after the beam has left the machine, allowing a filter to be chosen to reduce the energy traveling through the tube to a desired amount of energy to treat the patient. A method of controlling the amount of energy to reach a breast cancer patient undergoing electron radiation therapy includes selecting a filter made of a material having substantially the same density as human tissue and placing the filter between an intraoperative electron radiation therapy machine and a breast cancer patient to change the energy of a monoenergetic beam after it has left the machine, the filter being chosen to reduce the energy traveling from the machine to a desired amount of energy to treat the patient.

Description:
CROSS-REFERENCE TO RELATED APPLICATIONS 
     Priority of U.S. Provisional Patent Application, Ser. No. 61/777,286, filed on Mar. 12, 2013 and incorporated herein by reference, is hereby claimed. 
    
    
     STATEMENT REGARDING FEDERALLY SPONSORED RESEARCH OR DEVELOPMENT 
     Not applicable 
     REFERENCE TO A “MICROFICHE APPENDIX” 
     Not applicable 
     BACKGROUND OF THE INVENTION 
     1. Field of the Invention 
     The present invention relates to Radiation Therapy. More particularly, the present invention relates to Intraoperative Radiation Therapy. 
     2. General Background of the Invention 
     Intraoperative Radiation Therapy (IORT) is the use of radiation to treat cancers during surgery. Two types of treatment exist: X-ray and Electron Beam. While there are numerous effective uses of both treatments, there are few that are considered either economically competitive or medically superior to alternative treatments. With the use of electron beam linear accelerators, teams around the world have proven that Intraoperative Electron Radiation Therapy (IOERT) is equivalent to External Beam Radiation Therapy or Intensity Modulated Radiation Therapy for early breast cancer. Moreover, it is believed to be six times more cost efficient, reducing the cost of treating certain cancers from $30,000 to $5,000 (anticipated Medicare reimbursement rate in 2014). 
     There are two reasons IOERT technology has not been adopted in the United States. First, the US Government does not reimburse the treatment through Medicare, preventing market participants from profiting from ownership. Second, the inability to share machines between hospitals limits the number of market participants to those that have the critical mass of breast cancer cases to provide IOERT services profitably. 
     Even when Medicare does begin reimbursement for IOERT, the number of cases required to provide IOERT services profitably, limits the market to extremely large hospitals since machines cannot easily be shared. Transportation allows hospitals to share the capital cost, allowing for even small hospitals to provide IOERT services profitably. 
     Medicare has not reimbursed the IOERT market for many reasons, but from a practical point of view reimbursement would cause a misallocation of capital since the current class of IOERT machines are unable to be transported between hospitals efficiently. Although they claim to be transportable between hospitals, the machines must be calibrated for at least three energies of the machine to ensure proper function according to some studies. In the end, this amounts to three energies and multiple collimators to create different treatment fields. Prior to use of the machine on a patient one must test at least the energy being delivered for surgery and the ability to change the beam to one energy above and below the prescribed dose. This type of testing is called calibration. Calibration must be done every time the machine is moved between hospitals to ensure it is working in the way intended. 
     One can find boluses for use in radiation therapy at the following website: http://www.dotdecimal.com/products/ect. The following patent references are incorporated herein by reference: U.S. Pat. No. 8,094,779, U.S. Pat. No. 8,073,105, U.S. Pat. No. 5,037,374, U.S. Pat. No. 6,381,304, U.S. Pat. No. 7,834,336, U.S. Pat. No. 8,106,371. 
     BRIEF SUMMARY OF THE INVENTION 
     It is believed that Precision Accelerators&#39;s machines will be three times as fast as the prior art machines in terms of calibration. Every time a prior art machine that varies its energy powers up after transport, it must be tested at three different energies to show that the machine is working. Precision Accelerators&#39;s machine can only produce one energy and thus need only be calibrated to this single energy. All else being equal, removing energy variation in the head of the machine and moving it to the end of the collimator tube produces effectively the same treatment beam without having to calibrate the machine ad nauseum. 
     Inter-hospital transportation necessitates extremely quick calibration and quality assurance. The easiest beam to calibrate is a monoenergetic beam that is modified after the beam window because beam modification does not have to be included in linear accelerator quality assurance except as an attachment, which is tested at the same time the machine energy is. This saves a great deal of time because, instead of having to perform 5 tests for three different energies for a total of fifteen (15) tests, there are only five tests for one energy: 200 MU Test, 1000 MU/min test, and three tests of the 10 MeV beam with bolus output to verify beam. 
     The present invention includes two previous ideas put together in a unique way. The invention, although inspired by public ideas, is not obvious. Otherwise, the other manufacturers of machines on the market would simply have redesigned their machines with only one energy and modified the beam using a bolus to allow for transport. They never viewed their energy modification as a problem. Rather, they tout their technical prowess as a feature. The fact that one such competitor attempted to transport IOERT machines between hospitals, but after many attempts conceded that IOERT linear accelerators are not able to be effectively transported, demonstrates that they were unable to figure out a solution to both problems: beam stability and transportability. If the present invention were obvious, this competitor would have implemented it before now. 
     A third-generation of machines, see for example http://www.newrt.com/en/products/novac-11.html, uses collimators in order to create a homogeneous electron beam. These machines have a small, concentrated electron beam unsuitable for medical purposes coming out of the linear accelerator head that is transformed into a homogeneous, distributed beam as it runs through the length of the tube. This happens because of a repelling interaction between electrons within the tube, forcing the electrons to become evenly spread out while they travel through the tube. The Lucite brand poly(methyl methacrylate) tubing the collimator is made of absorbs aberrant electrons with minimal x-ray generation. After passing through a small amount of plastic film around the end of the tube before the breast that is meant to flatten the tissue, the electrons penetrate the potentially cancerous tissue on the surface of the breast, irradiating any remaining cancerous tissue. 
     A separate, but equally useful, invention is the tissue compensator aka a bolus to replace tissue (see, for example, the following website: http://vetmed.illinois.edu/4dvms/documents/imaging/RadTherapy/Overview.pdf). These are employed in radiation therapy to create a more homogeneous energy distribution in uneven tissue by compensating for any missing tissue. This is accomplished by inserting material that is of the same density as human tissue to compensate for the missing tissue. This technology can be employed for any type of radiation as the physics behind it are very simple: every 1 MeV of energy is an extra ½ cm to ⅓ cm of tissue penetration, depending on the exact density of the material chosen. The material chosen will be determined by empirical testing to decide which material gives the best results. The material is typically and preferably tissue isodense poly(methyl methacrylate). However, any hypo- or hyperdense material could be used in the same way, but one would need to take into account the difference in density between the human tissue and the material used. 
     While these two ideas have existed separately on the marketplace for many years, there has been no reason to put the ideas together because there was no application for isodense material before, after, or within a collimator tube for breast IOERT except as a means to increase the dosage to the skin. Even after three generations of machines, companies producing the prior art machines choose to use an electronic system of attenuating beam energy because they apparently believe this is the best way to vary energies in IOERT devices despite its higher cost and increased complexity. They did not choose modification of the electron beam through a compensator though it would produce results. Other manufacturers apparently simply do not see the advantage of this method over electronic variation. 
     An alternative method (an embodiment of the present invention) of attenuating the energy of an electron beam is to place isodense material (an isodense filter) in the path of the beam before it hits the tissue. By placing material in the way of the beam, there is the same effect of reducing the electron beam energy. Every 1 cm of isodense material reduces the depth the beam penetrates the tissue by about 1 cm. This is the same as reducing beam energy by about 3 MeV since the beam is penetrating the same amount of material of the same density. The actual radiation dose is determined by the output of the machine head as measured by dosimeters; however the depth of penetration is determined by the energy of the electron beam or, in the present invention, by the use of bolus not the energy (and thus speed) of the electrons in the beam. The only difference between an electrically-modulated beam with a bolus to remove the skin-sparing dose and a pure bolus system is calibration time. The treatment is otherwise identical. The compensator/bolus thickness for materials of densities other than that of human tissue will vary and are not standardized. By combining these interchangeable compensators/boluses of varying thicknesses with industrial electron linear accelerators, one can create a medical-grade, transportable linear accelerator. The bolus collimator is, in effect, creating transportable, stable, industrial-strength, robust linear accelerators for medical use out of industrial linear accelerators since what really makes an electron beam therapy device a medical device is the ability to vary the dose from patient-to-patient. 
     A very clear advantage of using a bolus as opposed to electronic variation is that the air/tissue interface is effectively moved away from the tissue being treated and is instead present at the air/isodense material interface. In this manner the skin-sparing dose is moved away from the tissue being treated. This allows all of the tissue being treated to receive 100% of the prescribed radiation dose. In the case of external beam compensation, the skin-sparing dose is desirable because there is skin which is highly sensitive to radiation between the beam and the cancerous tissue. Since the skin is treated in external electron beam, it is desirable to minimize the dose the skin receives. However, since IOERT is performed when the skin is not in the way of the beam, there is no need for this skin-sparing dose. Accordingly, there is no negative effect, and arguably a positive effect, associated with having a large compensator in front of an electron beam used in breast IOERT treatment. 
     An advantage of the present compensator based mechanism for changing the depth of penetration of the operative electron beam method is the calibration efficiencies. Originally, calibration efficiencies were not a concern because the stationary machines were in a dedicated, shielded room and did not need to be calibrated daily. Upon invention of intra-hospital mobile devices, the patient-treatment volume did not require the current manufacturers to solve the problem of radiation safety limits from frequent, radiation-intensive calibration, which lowers the maximum number of patients. The best solution to the problem of the inversely correlated nature between patient number and radiation exposure is to minimize unnecessary radiation exposure. In other words, the only way to increase patients is to reduce calibration time, thereby reducing the radiation used in the process. Since patient treatment and machine calibration are both components of the allowable total machine usage in a given day, one can increase the patient volume by decreasing the time required for calibration of the machine 
     Suitable materials for this isodense filter include isodense materials made up primarily or entirely of carbon, oxygen, and hydrogen, such as: poly(methyl methacrylate) (PMMA—a transparent thermoplastic sold under the trademarks Lucite, Plexiglas, and Perspex, for example), Delrin brand acetal resin, UHMW (ultra-high molecular weight polyethylene), polyethylene, polypropylene, ABS, acrylic, Bakelite, CPVC, fiberglass, Kynar brand plastic, Lexan brand plastic, Micarta brand plastic, PVC, Ryton brand plastic, and Teflon brand polytetrafuoroethylene, when the tissue is human breast tissue. Tissue compensators used for electron beam preferably require low atomic number materials so as to minimize the amount of Brehmstrahlung x-rays that are created. 
     While preferably the density of the isodense filter is the same as the tissue which is being radiated, the density could vary, though preferably not more than 2% so as to not dramatically change the tissues treated. 
     While virtually any material can be used as a collimator filter in the present invention, it is preferable that the density is the same as human tissue or roughly that. This makes it easier in two ways. First, if a patient has a breast that needs to be treated to a depth less than the 3.3 centimeters (the 10 Mev electron beam by definition has a 90% isodose line of penetration located at 3.3 cm), a corresponding filter could be used to reduce the amount of penetration by the level that would be required to move the tissue penetration less deeply in the tissue. For example if an oncologist wishes the 90% isodose line to be at 2.3 centimeters in the breast rather than 3.3 cm he can prescribe a 1 cm tissue isodense bolus to bring the 90% isodose line to 2.3 centimeters. There is minimal math needed. Second, there are many isodense materials available for manufacturing, such as poly(methyl methacrylate), which is desirable because it is inexpensive plastic. One can make many boluses cheaply from this material. 
     The bolus is preferably a solid shape which may be attached to a collimator of preferably isodense material. The bolus is preferably a solid cylinder of isodense material, such as plastic, and preferably Lucite. It is preferably attached to a hollow cylinder of Lucite (the collimator tube). Preferably, the bolus and hollow cylinder are integral. Calibration for the 10 meV beam would preferably be done at 100 cm source surface distance. The additional bolus would in the preferred embodiment be added to create a dosimetrically equivalent beam when less penetration is desired. This makes variation of depth penetrance simple and intuitive for the radiation oncologist. To move the 90% isodose line 1 cm less in tissue, one can advantageously use a 1 cm tissue isodense material duplicating the dosimetric characteristics of a 7 MeV electron beam. To duplicate a 6 MeV electron beam one could use a 1.3 cm attenuator. This actually allows for more precise dosimetry than is currently available since the depth of the 90% isodose curve may be moved in smaller increments. 
     Other machines have a computer and electronics which are subject to malfunction, varying the energy of the beam. Precision Accelerators is the only company to only change the characteristics of the beam after it has come out of the head of the IOERT machine. This makes the Precision Accelerators machine extremely stable. 
    
    
     
       BRIEF DESCRIPTION OF THE SEVERAL VIEWS OF THE DRAWINGS 
       For a further understanding of the nature, objects, and advantages of the present invention, reference should be had to the following detailed description, read in conjunction with the following drawings (which, for ease of illustration, are not to scale), wherein like reference numerals denote like elements and wherein: 
         FIG. 1  is a perspective view of a preferred embodiment of the apparatus of the present invention; 
         FIG. 2  is a detail of a preferred embodiment of the apparatus of the present invention (not to scale); 
         FIG. 3  is a top view of a preferred embodiment of the apparatus of the present invention in use; 
         FIG. 4  is a perspective view of a preferred embodiment of the apparatus of the present invention showing it ready to be used with a supine patient; 
         FIG. 5  is shows a prior art IOERT system (not to scale); and 
         FIG. 6  shows a prior art IOERT system (not to scale); 
         FIG. 7  is a detail of a prior art system. 
     
    
    
     DETAILED DESCRIPTION OF THE INVENTION 
     In order to provide for a multiple energy linear accelerator using a single energy machine, multiple collimators can be created with boluses  21 - 27  of many different thicknesses to provide doctors with the most treatment flexibility. Ideally, there will be a series of seven removable collimator tubes  15  with boluses  21 - 27  (preferably integral with tube  15 , but boluses  21 - 27  could instead be suitably attached in some fashion which would not allow leaking of the beam around the boluses  21 - 27 ), along with a tube  15  without a bolus in the event that the full energy of the monoenergy beam is desired for treatment. With seven boluses of 0.333 cm increasing increments, the beam energy (and thus speed of electrons) can be changed from 10 MeV (no bolus) to 9 MeV (0.333 cm material) all the way to 3 MeV (2.333 cm material). Below a beam energy of 3 MeV, the beam does not penetrate even 1 cm of breast tissue, too low energy to be therapeutic in most cases. The bolus  21 - 27  is preferably a solid cylinder of isodense material, such as plastic, and preferably Lucite. It is preferably attached to a hollow cylinder of Lucite (the collimator tube  15 ). Preferably, the bolus  21 - 27  and hollow cylinder  15  are integral. 
     While perhaps the bolus could be placed at any area in the length of the tube, it is preferred to place the bolus  21 - 27  at the end of the tube  15  closest to the breast, which will provide the patient with the most homogeneous electron beam for treatment as the beam has run the entire length of the typically 100 cm hollow tube  15  before reaching bolus  21 - 27 . In addition the flattening and the symmetry of the beam is at the end of the collimator since there would be some Brehmstrahlung x-rays generated by interaction with the bolus and the calibration would be greatly complicated. 
       FIG. 1  is a perspective view showing a preferred embodiment of the present invention, IOERT apparatus  10 . Apparatus  10  includes an IOERT machine  11 , which could be a simple, relatively non-expensive mono-energy industrial linear accelerator which produces 10 MeV of radiation. Machine  11  is preferably an industrial, durable, accelerator with technology stable enough for transport from hospital to hospital. A collimator tube  15 , preferably made of PMMA (sold as Lucite, for example), is attached to the head  50  of machine  11  using a plastic tube  16  and a connector  19 . A plurality of boluses  21 ,  22 ,  23 ,  24 ,  25 ,  26 ,  27 , increasing in size from ⅓ cm to 2⅓ cm in ⅓ cm increments, is preferably included (though other sizes could be used to make the increments greater or smaller). These filters  21 - 27  are preferably made of isodense materials made up primarily or entirely of carbon, oxygen, and hydrogen, such as poly(methyl methacrylate) (PMMA), Deirin brand acetal resin, UHMW (ultra-high molecular weight polyethylene), polyethylene, polypropylene, ABS (Acrylonitrile butadiene styrene), acrylic, Bakelite, CPVC (Chlorinated polyvinyl chloride), fiberglass, Kynar brand plastic, Lexan brand plastic, Micarta brand plastic, PVC (polyvinyl chloride), Ryton brand plastic, and Teflon brand polytetrafluoroethylene, when breast tissue is being treated. Preferably, the boluses  21 - 27  are integral with tube  15 , and the distance from the top  14  of tube  15  to the top of the boluses  21 - 27  (as shown in  FIG. 1 ) is the same for each tube  15  and bolus (100 cm, for example). Thus, for example, the total length of tube  15  and bolus  21  would be 100⅓ cm, and the total length of tube  15  and bolus  27  would be 102⅓ cm. 
       FIG. 2  shows a detail of the present invention in use when treating the breast  31  of a human patient, with optional cling wrap  17  over the distal end of collimator tube  15  and a bolus  24  which is preferably integral with tube  15  and is present at the distal end of collimator tube  15  to reduce the radiation entering the breast  31  from 10 MeV to 6 MeV. 
     In  FIG. 3 , apparatus  10  is shown in use to treat a breast  31  of a patient. A bolus  25  is shown integrally attached to tube  15 . Optional cling wrap  17  is shown over the distal end of bolus  25 . Bolus  25  will reduce the radiation reaching breast  31  from 10 MeV to 5 MeV (as 5 MeV of energy will be dissipated as the electrons flow through bolus  25 ). Treatment area  42  extends 1⅔ cm into breast  31  in this example, as bolus  25  is 1⅔ cm thick (as shown in  FIG. 5 , 10 MeV would normally extend 3⅓ cm into the breast  31 —the 1⅔ cm thick bolus  25  pulls 1⅔ cm of that energy region upward into bolus  25 , leaving just 1⅔ of breast  31  to be treated). 
       FIG. 7  shows a detail showing disposable plastic cling wrap  17  (which could be for example Glad brand cling wrap or plastic wrap by Saran) stretched over the end of tube  15  proximal the breast  31  (not shown) to flatten breast and/or minimize the chance of direct bolus contact with body fluids  31  and allow even penetration of the radiation from an IOERT machine. Cling wrap  17  could be used as well with the present invention, though when boluses  21 - 27  are integral with tube  15 , the boluses would flatten breast  31  and allow even penetration of the radiation from an IOERT machine, even without cling wrap  17 . 
       FIGS. 5 and 6  show prior art IOERT systems in which the amount of radiation reaching the breast  31  is controlled electronically, rather than with the use of boluses  21 - 27  of the present invention. As can be seen in  FIG. 5 , a 10 MeV beam will typically penetrate and treat 3⅓ cm of breast  31  tissue, while a 6 MeV beam (see  FIG. 6 ) will typically penetrate and treat 2 cm of breast  31  tissue. 
     While theoretically one can use just about any type of material for boluses  21 - 27 , it is best to use an isodense material (a material which has roughly the same density as human breast tissue) because it avoid some problems of other densities. With an isodense material such as poly(methyl methacrylate), little math is needed to determine how much to use; one simply determines the amount of attenuation desired and selects the collimator tube  15  with the bolus  21 - 27  that corresponds to that attenuation (bolus  21  for 1 MeV, bolus  22  for 2 MeV, etc.). 
     If one uses a material with a high atomic number like lead, more of the radiation will be transformed into Bremsstrahlung, through the interaction of the treatment beam electrons with the nucleus of the molecules they pass by in the bolus. Brehmstrahlung is produced when the electron beam hits the tissue, but this happens regardless of the method of energy attenuation. Bremsstrahlung is just a statement of the conservation of energy in an indirect manner. When the electrons have their energy and/or direction changed, some of this energy is released in the form of other radiation, like heat or x-rays. This is Bremsstrahlung. One wants to minimize this during radiation treatment since Bremsstrahlung is a more penetrating form of radiation and has much greater shielding requirements 
     If one uses too dense a material, there are two problems: 1) the precision of the width of the bolus increases dramatically (if one used an extremely dense material, the difference between boluses would be measured in mm, not cm) and 2) more Bremsstrahlung radiation is created. Imagine electrons going into a tight net. The larger the atomic number and thus atoms, the smaller the holes. With smaller holes, more electrons hit the net, causing the string to vibrate. In this example, the vibrations would be Bremsstrahlung. 
     Using a material that is less dense than tissue theoretically could be advantageous as there is less decelerating radiation because there are lower atomic number atoms involved and thus smaller nuclei. Ideally, if Bremsstrahlung were the only concern, one would want to use hydrogen gas compressed to a density near that of tissue as this would produce the least Bremsstrahlung since hydrogen is the smallest nucleus in the universe known to man. Unfortunately, hydrogen gas is highly explosive and not suitable for this purpose. While using other gases would work as well, this method is cost prohibitive because the manufacturing process would be much more complicated than injecting Lucite into a mold. In addition to higher manufacturing costs, the compressed-gas bolus would be extremely prone to breaking if dropped as it is hollow with a highly compressed gas inside, unlike Lucite which is a solid block of plastic. Moreover, most doctors use isodense material and it is the standard, therefore no real research has been done into a hypodense bolus. 
     The collimator filters or boluses  21 - 27  can be held in place on the distal end of tube  15  with a simple t-bone clamp (such as that shown in http://www.hclfasteners.com/shoppdfs/t-bolt.pdf). This method helps to ensure that there a tight fit that is perfectly aligned with the end of the collimator tube  15 . It is preferable for the collimator filters  21 - 27  to have a diameter substantially equal to the outer diameter of tube  15  so that all or substantially all radiation traveling through tube  15  likewise travels through a filter  21 - 27  (otherwise, there could be areas where the radiation would go deeper into the patient&#39;s tissue than desired). The present inventor believes that the best way to achieve this is to simply make the collimator filters  21 - 27  integral with collimator tube  15 . Other possible, but not preferred, means of attachment of boluses  21 - 27  to tubes  15  include a screw-on bolus, tape to hold the bolus on, a t-bolt clamp, or even the right size thick rubber band. The problem with all of these methods is that they introduce human error, which can be just as dangerous as computer error. Therefore, the preferred means of attachment that maintains the safety of removing a computer, while not introducing any other errors, is making the bolus part of the collimator. 
     The diameter of collimator tube  15  and collimator filters  21 - 27  can be, for example, about 1-30 cm, preferably about 2-25 cm, more preferably about 3-15 cm, and for example about 5 cm or 10 cm. The length of collimator tube  15  can be, for example, about 95.5-104.5 cm, preferably about 98-102 cm, more preferably about 99-101 cm, and for example about 100 cm. 
     Precision Accelerators will have a machine that is more stable and more precise because it uses a physical method of modulation. As long as its PMMA boluses  21 - 27  are accurate enough, the apparatus  10  will modulate the beam better, without need for extensive electronics, than the current methods do allowing for transportation. The present inventor believes that all competitors of Precision Accelerators use a method of varying their energy that is directly proportional to beam error bands. This is because electronically varying the current cannot go below a certain unit of accurate variation. This is what every system uses. Precision Accelerators&#39;s physical method is a more precise method of varying the exact electron energy and direction because it is physically verified and therefore has no error. The beam variation is reduced to insignificant levels for virtually no additional cost, while increasing the features of the machine to daily inter-hospital transport. While the difference is subtle, the means of variation has a large impact on the way Precision Accelerators&#39;s machine is used, increasing efficiency. 
     The present inventor believes that the best way to join a bolus  21 - 27  to the tube  15 , which must be confirmed by testing, is to make the bolus  21 - 27  integral with the collimator tube  15  when molding the tube  15 . This allows the system to use existing interlocks and not have to engineer anything else. Moreover, it is very difficult to lose or break a 100+ cm tube of thick plastic. Therefore, it is highly unlikely that this will be lost. As long as this is not inefficient in setting up, this is most likely the best because there will be no parts lost. 
     PARTS LIST 
     The following is a list of parts and materials suitable for use in the present invention: 
     Parts Number Description 
     
         
           10  IOERT apparatus of the preferred embodiment of the present invention 
           11  IOERT machine (such as an industrial linear accelerator, such as a 10 MeV Portac model produced by L&amp;W Research Inc. of Connecticut—http://www.lwresearch.com/products/portae/portac.html) 
           14  connector between tube  15  and tube  16   
           15  plastic collimator tube (such as PMMA) 
           16  plastic tube connecting collimator tube  15  to IOERT machine  11   
           17  plastic cling wrap placed over proximal (to patient) end of tube  15  to flatten breast  31   
           18  connection when boluses  21 - 27  are not integral with tube  15 —otherwise, boundary between open tube  15  and boluses  21 - 27  when tube  15  and boluses are integral 
           19  connector between tube  16  and IOERT machine  11   
           21  ⅓ cm thick bolus (such as PMMA) 
           22  ⅔ cm thick bolus (such as PMMA) 
           23  1 cm thick bolus (such as PMMA) 
           24  1⅓ cm thick bolus (such as PMMA) 
           25  1⅔ cm thick bolus (such as PMMA) 
           26  2 cm thick bolus (such as PMMA) 
           27  2⅓ cm thick bolus (such as PMMA) 
           31  human breast being treated for cancer 
           41  region of skin-sparing dose 
           42  region of 100% energy at 10 MeV 
           43  region of 100% energy at 6 MeV 
           50  energy producing head of IOERT machine  11   
       
    
     All measurements disclosed herein are at standard temperature and pressure, at sea level on Earth, unless indicated otherwise. All materials used or intended to be used in a human being are biocompatible, unless indicated otherwise. 
     The foregoing embodiments are presented by way of example only; the scope of the present invention is to be limited only by the following claims.