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   1 lf-absorption effect, typical for low-energy beta particles.                                         
     2 f secondary electrons in c-Si by the primary beta-particles.                                         
     3  varied significantly in their absorption of beta-particles.                                         
  
     5 ionuclides that emit low-energy electrons or beta particles (169Er, 117mSn, and 33p) were evaluated. 
     6 tent cytotoxicity of alpha-particles than of beta-particles, (211)At-labeled agents may be ideal for 
     7  increase the steady-state level of apo B100-beta particles above that of apo B100 particles in contr
  
     9 bution of a radioisotope that emits alpha or beta particles, and show empirically that the null funct
  
    11 the Au-198 isotope; the range of the (198)Au beta-particle (approximately 11 mm in tissue or approxim
    12 gations, recent calculations have shown that beta particles, because of their helicity, radiolyse L- 
    13 tion of whether absorption and scattering of beta-particles by stent struts will cause significant pe
  
  
    16  models, radionuclide S values (electron and beta particle components only) were subsequently calcula
  
  
  
  
  
  
    23 EG) chains linked to DOTA for complexing the beta-particle emitter (177)Lu and to panitumumab for tar
    24 notherapy with these bsRICs labeled with the beta-particle emitter (177)Lu or the Auger electron-emit
  
    26 stantial dosimetric advantage over energetic beta-particle emitters (e.g., 32p, 89Sr, 186Re) for irra
    27 delivered by Ab LL1, both Auger electron and beta-particle emitters can produce specific and effectiv
    28  a large dosimetric advantage over energetic beta-particle emitters for alleviating bone pain, and po
  
  
    31  kill than other Auger electron emitters and beta-particle emitters, using an anti-CD74 antibody (Ab)
  
  
    34 as to evaluate the dose-related effects of a beta-particle-emitting radioactive stent in a porcine co
  
    36 Cerenkov luminescence, the light produced by beta-particle-emitting radionuclides such as clinical po
    37 ivo bremsstrahlung with the high-energy pure beta-particle-emitting radionuclides used for therapeuti
    38 rivascular space of vessels treated with the beta-particle-emitting stent compared with control vesse
    39 e of low-dose endovascular irradiation via a beta-particle-emitting stent inhibits neointimal formati
    40 estigate whether low-dose irradiation from a beta-particle-emitting stent would inhibit neointimal pr
    41 % versus 36.0 +/- 10.7%, P = .02) within the beta-particle-emitting stents compared with the control 
  
  
  
    45 erwent placement of 35 nonradioactive and 39 beta-particle-emitting stents with activity levels of 23
    46 166Ho with beta-emission (half-life, 26.8 h; beta-particle energies, 1.85 MeV [51%] and 1.77 MeV [48%
  
  
    49 rrow are comparable to the mean range of the beta particles for a wide variety of beta-emitting radio
    50    Moreover, autoradiography, which recorded beta particles from (198)Au, enabled visualizing the het
    51 ere obtained with only a few hundred emitted beta particles from the (90)Y/(90)Sr source or conversio
  
    53 biologic effectiveness equivalent to that of beta particles) from a low-dose rate 137Cs irradiator.  
    54  imaging system comprising a microchip and a beta-particle imaging camera permitted routine cell-base
    55 mity to the radioisotope convert the emitted beta(-) particles into photons having wavelengths in the
    56 erential response to the doses of continuous beta-particle irradiation used in this experimental mode
  
  
  
  
  
    62 t localizes in skeletal metastases and emits beta particles that may be therapeutically beneficial.  
    63 d with no therapy, alpha- ((149)Tb-cm09) and beta(-)-particle therapy ((161)Tb-cm09) resulted in a ma
  
  
    66 dition, the cross-fire effect of high-energy beta(-)-particles within the bone and the marrow may del
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