Therapy for Prostate Cancer: Technological and Clinical Aspects


Country

Who, where

Particle

S/C/SCa Max. energy (MeV)

Beam directions

Start of treatment

Total patients treated

Date of total

Canada

TRIUMF, Vancouver

p

C 72

1 horiz.

1995

175

Dec-13

Czech Republic

PTC Czech r.s.o., Prague

p

C 230

3 gantries, 1 horiz.

2012

140

Dec-13

China

WPTC, Wanjie/Zibo

p

C 230

2 gantries, 1 horiz.

2004

1,078

Dec-13

China

IMP-CAS, Lanzhou

C-ion

S 400/u

1 horiz.

2006

213

Dec-13

England

Clatterbridge

p

C 62

1 horiz.

1989

2,446

Dec-13

France

CAL, Nice

p

C165

1 horiz.

1991

4,936

Dec-13

France

CPO, Orsay

p

S 250

1 gantry, 2 horiz.

1991

6,432

Dec-13

Germany

HZB, Berlin

p

C 250

1 horiz.

1998

2,312

Dec-13

Germany

RPTC, Munich

p

C 250

4 gantries, 1 horiz.

2009

1,811

Dec-13

Germany

HIT, Heidelberg

p

S 250

2 horiz., 1 gantryb

2009, 2012

503

Dec-13

Germany

HIT, Heidelberg

C-ion

S 430/u

2 horiz., 1 gantryb

2009, 2012

1,368

Dec-13

Germany

WPE, Essen

p

C 230

4 gantriesc, 1 horiz.

2013

32

Dec-13

Italy

INFN-LNS, Catania

p

C 60

1 horiz.

2002

350

Dec-13

Italy

CNAO, Pavia

p

S 250

3 horiz., 1 vertical

2011

76

Dec-13

Italy

CNAO, Pavia

C-ion

S 480/u

3 horiz., 1 vertical

2012

105

Dec-13

Japan

HIMAC, Chiba

C-ion

S 800/u

horiz.c, verticalc

1994

8,073

Dec-13

Japan

NCC, Kashiwa

p

C 235

2 gantriesc

1998

1,226

Mar-13

Japan

HIBMC, Hyogo

p

S 230

1 gantry

2001

4,223

Dec-13

Japan

HIBMC, Hyogo

C-ion

S 320/u

horiz.,vertical

2002

1,935

Dec-13

Japan

PMRC 2, Tsukuba

p

S 250

2 gantries

2001

2,967

Dec-13

Japan

Shizuoka Cancer Center

p

S 235

3 gantries, 1 horiz.

2003

1,590

Dec-13

Japan

STPTC, Koriyama-City

p

S 235

2 gantries, 1 horiz.

2008

2,306

Dec-13

Japan

GHMC, Gunma

C-ion

S 400/u

3 horiz., 1 vertical

2010

985

Dec-13

Japan

MPTRC, Ibusuki

p

S 250

3 gantries

2011

919

Dec-13

Japan

Fukui Prefectural Hospital PTC, Fukui City

p

S 235

2 gantries, 1 horiz.

2011

428

Dec-13

Japan

Nagoya PTC, Nagoya City, Aichi

p

S 250

2 gantries, 1 horiz.

2013

199

Dec-13

Japan

SAGA-HIMAT, Tosu

C-ion

S 400/u

3 horiz., vertical, 45 deg.

2013

62

Dec-13

Poland

IFJ PAN, Krakow

p

C 60

1 horiz.

2011

39

Dec-13

Russia

ITEP, Moscow

p

S 250

1 horiz.

1969

4,320

Dec-13

Russia

St. Petersburg

p

S 1000

1 horiz.

1975

1,386

Dec-12

Russia

JINR 2, Dubna

p

C 200d

1 horiz.

1999

995

Dec-13

South Africa

NRF—iThemba Labs

p

C 200

1 horiz.

1993

521

Dec-13

South Korea

NCC, IIsan

p

C 230

2 gantries, 1 horiz.

2007

1,158

Dec-13

Sweden

Uppsala

p

C 200

1 horiz.

1989

1,356

Dec-13

Switzerland

PSI, Villigen

p

C 250

2 gantriese, 1 horiz.

1984, 1996, 2013

7,045

Dec-13

USA, CA

Loma Linda

p

S 250

3 gantries, 1 horiz.

1990

17,829

Dec-13

USA, CA

UCSF

p

C 60

1 horiz.

1994

1,621

Dec-13

USA, MA

NPTC, MGH Boston

p

C 235

2 gantriesc, 1 horiz.

2001

7,345

Dec-13

USA, IN

IU Health PTC, Bloomington

p

C 200

2 gantriesc, 1 horiz.

2004

1,927

Dec-13

USA, TX

MD Anderson Cancer Center, Houston

p

S 250

3 gantriesc, 1 horiz.

2006

4,746

Dec-13

USA, FL

UFPTI, Jacksonville

p

C 230

3 gantries, 1 horiz.

2006

5,085

Dec-13

USA, OK

ProCure PTC, Oklahoma City

p

C 230

1 gantry, 1 horiz, 2 horiz/60 deg.

2009

1,364

Dec-13

USA, PA

UPenn, Philadelphia

p

C 230

4 gantries, 1 horiz.

2010

1,744

Dec-13

USA, IL

CDH Proton Center, Warrenville

p

C 230

1 gantry, 1 horiz, 2 horiz/60 deg.

2010

1,329

Dec-13

USA, VA

HUPTI, Hampton

p

C 230

4 gantries, 1 horiz.

2010

767

Dec-13

USA, NY

ProCure Proton Therapy Center, New Jersey

p

C 230

4 gantries

2012

512

Dec-13

USA, WA

SCCA ProCure Proton Therapy Center, Seattle

p

C 230

4 gantries

2013

86

Dec-13

USA, MO

S. Lee Kling PTC, Barnes Jewish Hospital, St. Louis

p

SC 250

1 gantry

2013

1

Dec-13

USA, CA

Scripps Proton Therapy Center, San Diego

p

C 250

3 gantries, 2 horiz.

2014

1

Feb-14


Particle therapy facilities in operation: Information about technical equipment and patient statistics. Last update: 24 March 2014

a S/C/SC = Synchrotron (S) or Cyclotron (C) or SynchroCyclotron (SC)

bWith beam scanning

cWith spread beam and beam scanning

dDegraded beam

eWith beam scanning, Gantry 1 since 1996, Gantry 2 since 2013



Nowadays, protons are an accepted treatment modality for tumors in difficult to treat locations, i.e., in the area of the skull base or along the spinal axis, also including sarcomas involving the thoracic chest wall, as well as malignancies in pediatric patients, where minimizing normal tissue radiation exposure is of paramount importance. Outcome analyses demonstrate very satisfying tumor control rates and at the same time low incidence of radiation-induced toxicities (Hug and Slater 2000; DeLaney et al. 2009; Rutz et al. 2008).



3 Physical Characteristics of Protons


PT with its physical characteristics of superior dose deposition in a given tumor and reduced radiation dose to surrounding normal tissues offers an inherent geometric advantage. Lower entrance doses as well as sharp dose falloff at the distal edge of the beam result in a significant higher conformality in comparison to photons. The main disadvantage of the proton beam is the worse lateral dose falloff and the range of uncertainties when treating tissues of different densities especially if there are inter- and intra-fractional changes during treatment (Fig. 1).

A304279_1_En_1018_Fig1_HTML.jpg


Fig. 1
Dose distribution of different beam qualities


4 Radio-Biological Effectiveness (RBE) of Protons


According to the International Commission on Radiation Units and Measurements (ICRU) report 78 (ICRU 2007) the radio-biological effectiveness (RBE) of protons is comparable with the RBE of photons. Dose units expressed as physical dose have a difference of about 10 % in favor of protons (Paganetti et al. 2002). The usually constant RBE of 1.1 in comparison to photons is an advantage of the proton beam. Nevertheless, one has to estimate a higher RBE at the distal edge of the proton beam. Also, the intensity of the linear energy transfer (LET) influences the RBE (see also the following chapter “There is Evidence of the Superiority of Protons or Heavy Ions, Pro”). Comparable proton or photon doses have a similar cell-killing effect on tumors and similar toxic effects on normal healthy tissues (Paganetti et al. 2004). This results in an excellent estimation of expected toxicities in comparison to applied doses during the treatment planning process. Established tolerance doses in RT are generally transferable to PT. All available publications on treatments with protons confirmed it. No publication has raised the issue of unexpected acute or late toxicity. Any described incidence of late toxicity was related to high dose escalation rather than use of protons. The initial concept of physical dose distribution and effectiveness has not been called into question by clinical results. However, no phase III trials were available comparing protons and photons. Most proton radiation therapy data were based on retrospective reviews and only for a few indications data were based on phase I/II trials of single institution experiences. Multi-institutional collaboration was very limited.

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Oct 1, 2016 | Posted by in GENERAL RADIOLOGY | Comments Off on Therapy for Prostate Cancer: Technological and Clinical Aspects

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